System and methods to track and increase muscle efficiency

ABSTRACT

An object of the present invention is to provide a system and method of determining muscle efficiency and inefficiency in a patient or subject and being able to quantitatively determine measurements that communicate between practitioners the condition, the health, and the efficiency state of any muscle. The efficiency of a muscle is defined by the ability of the brain to bridge a proper communication to the muscle by sending normal action potentials; the bridge is often compromised during injury, improper training, or from poor habits of bodily movement. The standardization of these efficiencies allows for the isolation of particular areas of the muscles that are inefficient and efficient. Further, with varied application of electrical pulses, a bridge that mimics the natural action potential is provided and can enhance muscle efficiency in a way that achieves higher levels of success in bodily healing and physical training than in any prior art. The current invention uses multiple, select sets of electrical currents at sound wave frequencies with specific forms of movements. The application of electrical currents can also be synchronized with extensions and contractions of muscles to stimulate the expedited bridging of brain to muscle and increase the efficiency of muscles. The current invention discloses a system to deliver these electrical currents and offers the capabilities to standardize these techniques to reconnect the brain to these muscles to an efficient level.

TECHNICAL FIELD OF THE INVENTION

The invention relates to the use of multiple sets of electrical waveshaving sound wave frequencies that allows one set of waves to sync withthe body and at least one other set of pulsed sound waves to harmonizewith and stimulate the nervous system in a manner that, when combinedwith specific forms of exercises, leads to recognition of efficiency inthat muscle and ways to standardize the measurement of muscle efficiencyand to increase muscle efficiency in those selected muscles. By creatingparameters for measuring efficiency in muscles, a system is derived thatallows users to determine muscle efficiency and track improvements inmuscle efficiency during treatments. The treatments are designed tobridge communication between the brain, nervous system, and muscles bymimicking the natural action potentials of the human nervous system.Many unexpected derivative methods of building muscle efficiency andsystems that are used in conjunction are described below.

BACKGROUND OF THE INVENTION

Despite modern advances in medicine and medical equipment, sophisticatedtechniques to accelerate the basic biological processes of healing andtraining are only now being discovered. In the fields of training andhealing muscles, using a few particular movements combined withelectrical stimulation is well known, but the current invention uses twoor three specific electrical direct currents using sound wavefrequencies to mimic voltage waveform patterns of an action potential.When done with a very particular set of bodily movements, the bridgingof communication between the brain and muscles allow the muscles toincrease their efficiency, which results in accelerated results inhealing and training that have surprising statistical significance. Whatis more unexpected is that the inventors have been able to quantify thisinefficiency in muscles based on data from the use of these electricalcurrents and precise movements of the body that allows a new way ofstudying physiology and categorizing muscle healing and development.

Introduction

The human body has evolved to react to different environmentalconditions in an efficient manner. A scrape on the arm immediatelytriggers the body to address the wound by coagulating the blood andinitiating the white blood cell response. A developing athlete with anew interest in basketball quickly builds a connection between thecomplicated neuronal instructions and a diverse set of muscles thatconstantly adjusts when the athlete is learning new skills or growingstronger.

Science has advanced medicine and immunology in many ways, butover-confidence in modern techniques has in many ways deterred researchin processes that involve natural, biological ways of healing andgrowing. Let's take the example of a knee injury. A common knee sprainmay involve the swelling and inflammation in and around the knee's majorligaments. This knee injury also triggers a response in which the bodychanges output to the muscles around that knee. This response actuallyweakens the leg, because the inability to contract or release thesemuscles reduces the functional ability of that leg. In particular, thereis a reduction in that leg's ability to absorb force. The muscles suchas the hamstrings, quads, and calves around the knees become less ableto support the joint, permitting more force to be placed back on theinjured joints and ligaments and actually increasing the risk ofre-injury. These muscles are reduced in efficiency because of changes infunction of the controlling aspects of the brain and nervous system,which begin to provide fewer stabilizing pulses to these muscles. Thesepulses are well known in the science community as “action potentials.”

Historically, this simple concept is misunderstood. Because of injuriesto the cells in damaged areas, many researchers have mislabeled theproblem as cellular disruptions. There is no empirical evidence thateruption of cells directly cause the lack of efficiency in thesemuscles. Because the lack of efficiency in muscles results from lack ofuse as well, even non-injured muscles that are misused or unequally usedalso show the same type of muscular inefficiency. And while someresearchers believe that the reversal of polarity in the cells directlyresults in the lack of muscle contractions or ability to effectivelycontract, there is no empirical evidence that polarity in an injury hasany significance to the science behind the lack of efficiency inmuscles. Thus, all that is known is that these muscles are reduced inefficiency.

The body depends on muscles to absorb force in most movements, butinjuries, such as knee injuries, impair this ability by reducing theefficiency of these muscles. Even when there is actually no damage tothe surrounding muscles, these muscles are reduced in efficiency as theinjury causes the body to change the pattern of using these muscles.Evolutionarily, this makes sense, because this signals the body to notuse the leg while we address the injury. However, it is a problem whenthese inefficiencies persist even after the injury is healed. Moderntechniques typically set the knee or cast it in an attempt to protect adamaged area, but immobilizing the knee further reduces the efficiencyof the whole leg's recovery.

This disclosure does not purport to invent the use of electricalcurrents to stimulate muscles. Even the use of multiple electricalfrequencies is well known in the industry and the use is in the publicdomain. For example, apparatuses in U.S. Pat. No. 4,374,524 to Hudek(1983) illustrates the use of a square-wave signal generator inconjunction with a plurality of phase-locked loops and low-pass filtersto produce a plurality of sine-wave, primary signals that can be used toactivate muscles. U.S. Pat. No. 4,071,033 to Nawracaj et al. (1978), andU.S. Pat. No. 4,153,061 to Nemec (1979) teach two primary signals ofdifferent frequencies and that also modulates amplitudes in primarysignals to achieve various therapeutic effects.

The use of direct current on the muscles, which is not well studied(because of historical difficulty of penetrating the outer skin to reachinner muscles using direct current), and using wave patterns thatresemble exponential waves is disclosed in U.S. Pat. Nos. 5,107,835 and5,109,848, which was published in 1992. These wave patterns purport toallow the highest levels of direct current to penetrate into the body,by using specific pulses wherein there exists one electrical waveformwith a set of sound wave frequencies overlaid with another electricalwaveform with a pulsed set of sound wave frequencies wherein the pulsedset of sound waves results in the treatment of muscles. In the end, thepulses are only designed to send pulses to the body. Althoughconventional A/C powered muscle stimulating devices trigger the actionpotential of a nerve, it does so by over-powering the ion channels thatproduce the action potential. There has never been an ability to provide(in-vivo) an electrical current that mimics an actual action potentialso closely that the body responds to it as if it was a real actionpotential. Up until now, there has never been a way to measure if thiswas even possible.

In U.S. Pat. No. 5,107,835, the inventor uses what they call a “periodicdouble exponential” wave pattern that relies on the use of multiplefrequencies and the use of wave shapes that are exponential. Althoughthis pattern of exponential characteristics has been proven clinicallyto address certain neuronal responses to muscles, the basis for whichthe inventors of the U.S. Pat. No. 5,107,835 patent relies on it workingis without supportive data.

U.S. Pat. No. 5,107,835 patent is described as “the substantiallyconstant amplitude periodic-exponential portion of the sum signal thatis applied to a patient's body by the apparatus” shows the shape of thisexponential wave characteristics. A reproduction of the prior art wavesignal is shown in FIG. 1. In particular, FIG. 1 shows the wave pattern82 that is the basis of U.S. Pat. No. 5,107,835. It uses electricalwaves and in baseline slope 102, there is no steady flat baseline;instead, the baseline is shown to be downward in slope. Downward slope102 is also named baseline 102. In baseline 102, there is no lowerwaveform signal that would represent a refractory period, or a downwardshape. If one existed, it would have the dotted line appearance in 103.There is a repeated pattern for sure, but because there is no flatbaseline or a refractory period downward bell shape of the wave indirect current, it lacks the type of shape that exists in nature, whichis namely the shape of an action potential. Studies have shown thatwithout reproducing the action potential waveform, the body may notfully respond to it as if it were a real action potential.

Thus, this wave pattern is not like the actual wave pattern ofelectrical voltage current experienced by the nerves. All cells inanimal body tissues are electrically polarized—in other words, theymaintain a voltage difference across the cell's plasma membrane, knownas the membrane potential. This electrical polarization results from acomplex interplay between protein structures embedded in the membranecalled ion pumps and ion channels. In neurons, the types of ion channelsin the membrane usually vary across different parts of the cell, givingthe dendrites, axon, and cell body different electrical properties. As aresult, some parts of the membrane of a neuron may be excitable (capableof generating action potentials), whereas others are not. Recent studieshave shown that the most excitable part of a neuron is the part afterthe axon hillock (the point where the axon leaves the cell body), whichis called the initial segment, but the axon and cell body are alsoexcitable in most cases.

Each excitable patch of membrane has two important levels of membranepotential: the resting potential, which is the value the membranepotential maintains as long as nothing perturbs the cell, and a highervalue called the threshold potential. At the axon hillock of a typicalneuron, the resting potential is around −70 millivolts (mV) and thethreshold potential is around −55 mV. Synaptic inputs to a neuron causethe membrane to depolarize or hyperpolarize; that is, they cause themembrane potential to rise or fall. Action potentials are triggered whenenough depolarization accumulates to bring the membrane potential up tothreshold. When an action potential is triggered, the membrane potentialabruptly shoots upward, often reaching as high as +100 mV, then just asabruptly shoots back downward, often ending below the resting level,where it remains for some period of time. This depression below theinitial level is known as the refractory period, during which themembrane's ions reorient themselves to once again establish the restingpotential. The shape of the action potential is stereotyped; that is,the rise and fall usually have approximately the same amplitude and timecourse for all action potentials in a given cell. In most neurons, theentire process takes place in about a thousandth of a second. Many typesof neurons emit action potentials constantly at rates of up to 10-100per second; some types, however, are much quieter, and may go forminutes or longer without emitting any action potentials.

FIG. 2 shows an action potential that is well studied and is consideredprior art for purposes of this disclosure, but the particular actionpotential in FIG. 2 is of an electrical voltage level over time of anaction potential in a human. This voltage wave pattern is not known tobe the model of any electrical current stimulation muscle device usingdirect current to sync with the nerve and therefore, the currentinvention involves models based on this waveform. There are many ways todescribe the scientific shape of a waveform. Depending on the type ofspecificity needed, these waveforms can have very specific names, butfor purposes of understanding what the shape of an action potential isand what the shape of current prior art electrical current machinesprovide, only simple terms are needed. FIGS. 3A-3F show various waveformshapes. In one general view, these can be considered the essential “sixtypes of waveforms” or “wave pattern shapes.” As shown by the U.S. Pat.Nos. 5,107,835 and 5,109,848 pattern, the waveform pattern they havedecided to use is an “exponentially decaying” which is similar to theclassic waveform of FIG. 3F. As shown by FIGS. 4A-4C, the known uses ofdirect current electrical current is currently in the exponentiallydecaying waveform as shown in prior art FIG. 5, which is the waveform ofthe initial peak and immediate voltage of the waveform used to create astimulus in prior art machines dating farther back than 1992. See U.S.Pat. Nos. 5,107,835 and 5,109,848, e.g. As shown in the downward slope501, the slope is in the shape of FIG. 3F, which is classically known asan exponential decaying waveform. The exponential decaying waveform isfollowed by a section that is considered to be the baseline 502, butunlike the action potentials of natural animals, there is no flathorizontal line, but rather a slow slope downwards. The distinction issignificant because it allows the body to have a state of equal balancewhich is a flat horizontal line, wherein the next action potential caninitiate, which is described in detail below.

But as shown in its disclosure, the pattern of waveform shape goesdrastically upwards in the next stage of a classic 1992 machine thatstimulates the body using direct current. As shown in FIG. 6, the nextstage of the prior art waveform usage uses a next peak 601 in thevoltage reading but has a sharp left turn 602:

In contrast, the downward slope of the waveform in the real actionpotential has more uniform downward shape as shown below in sections 701and 702 where even though it is a sharp decline, there are no near rightturns or 90 degree turns as shown in section 602 above. Even in sections703, there is a baseline formation that does not exist in the FIG. 6corresponding representation. Furthermore, FIG. 8 shows a standard “S”shape exponential rising to a peak wavelength form, and once again,there are no abruption angle changes that exits in section 602 of FIG.6, which is a 1992 prior art voltage meter reading of a direct currentfor the stimulation of muscles. FIG. 8 shows the next natural risingsection of a natural action potential. Section 801 does show a smooth Sformation wavelength, but section 802 shows a leveling off section.

The leveling off sections of the natural action potentials are noted,because they are clear distinctions from other uses of direct currenttreatments of muscles. The reason why there was a movement away from theuse of a wavelength that mimics the more natural action potential shapeis because of the previous misunderstood science.

Previously, the reasons for the force of stress being placed onligaments and joint tissues instead of muscles was believed to bebecause of a polarity creation in the injury. Because they werecharacterized as having cellular disruption sites wherein there was abreakdown in the polarized nature of these cells. In most cases, thismisunderstanding has hindered advancement in this field. Because theunderstanding that such direct current waves are needed to trigger thesestimulations, it was assumed that the polarized nature of the sitesafter treatment healed the cellular disruption sites. This is amisunderstanding.

What is understood is this: injuries lead to alterations in the usualfunction of muscles, making them inefficient. Because not all musclesbecome inefficient, there is a physiological different between musclesthat are inefficient and those that are efficient. When those two can becompared in an individual, a ratio of efficiency in muscles can bemeasured. When present, this inefficiency is due to the brain's reducedability to engage in the proper connection to the muscles. The musclesare generally controlled by action potentials, transmitted by the brainthrough the nervous system, that have a very specific shape. A furthercharacterization of these waveforms that mimic the waveform of an actionpotential differentiates from the 1992 use of direct current which wasonly designed to create pulses.

The use of direct current waveforms using electrical currents in two ormore sound wave frequencies can produce a natural action potentialformation. When this combination of wave forms is used to penetrate theskin and fats to reach the nerves, the result is a surprisingenhancement of muscle efficiency.

In addition, the waveform shape shows a patterned exponential risingshape that is uniform as shown in FIG. 8. The S shape of theexponentially rising curve has a leveling peak area at 802. There are noabrupt changes.

As shown in FIG. 2A of U.S. Pat. No. 5,107,835, the waveforms are akinto exponential decaying shapes and also are not similar to actual actionpotential voltage wave shapes. The real action potential has the purposeof creating an efficient means to send a message down to variousspecific muscles in as fast and as controlled a manner as possible. Indoing so, there is a baseline by which a specific shaped actionpotential voltage is sent down the nerve. Because of this specificshape, current science understands that the brain actually receivesfeedback from these action potentials. Imagine a boomerang: usingalternating current or even pulses of direct current to activate theaction potential does the job of contracting the muscle and telling thebrain that the muscle is contracted. That is equal to the throwing ofthe boomerang. What is needed and contemplated in this invention is theability to use or mimic natural action potential signals whichscientifically has been shown to provide feedback to the brain that thefiring of the action potentials has actually taken place. Then, it willbelieve that movement is being reported from the relevant muscles andwill respond to either “protect against” or allow that movement. Thisresponse gives insight into the efficiency of that muscle. There is nomistaking what the action potential shape is used for and the bodyrecognizes the natural form. Furthermore, the specific use to alterspecific forms of waves has not been studied in the use for increasingthe efficiency of muscles.

When the brain recognizes the natural form, it then has the ability toresync and re-engage that muscle, which by definition makes the musclesmore efficient. When the firing of the action potential is matched withthe nerves in a way that the brain believes that it is the real actionpotential, the feedback is akin to the matching of a thrown boomerang sothat the thrower can catch it and does catch it. In other words, thebrain receives the signal as if the muscle had been working on its own,and, in turn, learns to adopt this new, more appropriate way of usingthe muscles that it has been shown.

What is needed is a way to utilize the human body's naturally-evolved,biological processes for healing and strengthening, using moderntechnology not to outsmart the body, but rather to accelerate thesenatural processes by allowing the body to heal injury or enhance thefunction of the addressed muscles.

SUMMARY OF THE INVENTION

Although prior art methods have shown the use of electrical current,there are currently no methods that mimic the shapes of the waveformsthat exist in the human and animal bodies in a manner that penetrates tothe nerves. And there are no disclosed methods of fully using thesebiological conditions to help accelerate muscle efficiency orcommunicating within a community a reliable standard that can relaygeneral muscle efficiency in one person to another.

Initially, it is the object of the invention to derive a completelydifferent measurement for a qualitative measurement of muscleefficiency/inefficiency and a quantitative measurement of muscleefficiency/inefficiency and muscle state and progress. Because there hasnever been an ability to quantify muscle inefficiency, there had been noefforts to quantitatively describe parameters that chart the currentefficiency state of a muscle and the ability to communicate betweenpeople the status of the efficiency of the muscle and its health orfitness. It is an object of the invention to be able to measure theprogress of muscle efficiency in order to study statistical measurementsof various treatments using multiple sound frequencies of electricalwaves that bridge neuro-muscular communications so that measurements andstudies can be conducted in laboratory and clinical settings. It is anobject of the invention, therefore, to provide a system and methods thatresults in the ability to use multiple electrical waves in soundfrequencies that have the waveform that is more similar to the actionpotential of the nervous system. A further invention is the ability touse multiple frequencies in sound waves to create an additional nervousfeedback response to the brain so that the brain responds to it as itwould to a natural action potential. A further invention is the abilityto change the frequency of the actual waveforms and match it withfrequencies of the actual action potential the body would normally feelif the muscle was healthy, and to increase the power of that matchingfrequency in accelerated pathways such that during certain exercisemovements, there is a discernible match of the reproduced actionpotentials and natural action potentials. The coordinated specificmuscle movements with the invention disclosed further enhances therebridging of the brain's connection to these muscles that allows a muchhigher rate of improving muscle efficiency, which leads to acceleratedresults in healing and training. A further invention is the ability touse various forms of currents that are timed, coordinated with variousforms of exercises that are directed to engage the bridge between thebrain and the efficient use of muscles in accelerated forms. A furtherinvention involves the use of the standardized models of objective teststo get results from subjects that are unable to express differentdegrees of discomfort, the subjects include animals, infants, and peopleunable to communicate, such as comatose people. A further invention isthe specific application of these currents that allows for the extensionof muscles to support higher levels of muscle efficiency leading tohigher performance and faster results in training.

BRIEF DESCRIPTION OF THE DRAWINGS

For a more complete understanding of the present invention, and theadvantages thereof, reference is now made to the following descriptionstaken in conjunction with the accompanying drawings, in which:

FIG. 1 shows a prior art voltage reading of a direct current electricalcurrent used to stimulate the body that was well known by 1992.

FIG. 2 shows a classic form of action potential of a sodium ion channelnerve response showing the voltage with the action potential andrefractory period.

FIGS. 3A to 3F show six different shapes of waveforms wherein 3Erepresents a rising exponential waveform and 3F shows an exponentialdecaying waveform.

FIGS. 4A-4C shown prior art attempts of creating a pulse with a directcurrent showing peaks wherein none show any of the classic waveform asin the action potential, refractory period, and resting period to showthe response as shown in FIG. 2.

FIG. 5 shows a downward slope of a pulse used by direct current shown anexponential decaying waveform in a prior art system disclosed in 1992.

FIG. 6 shows an illustration of a peak following the downward slope inthe prior art system disclosed in the 1992 system.

FIG. 7 shown the downward slope of a natural action potential shown asharp decline in the exponential decay.

FIG. 8 shows another embodiment of a natural action potential shown an Spattern wherein a distinguishing element in a natural action potentialis the resting period and the ability to efficiently generate a quicksignal of varying degrees using the resting period as a baseline.

FIG. 9 shows another embodiment of the current system wherein muscleefficiency/inefficiency can be measured and treated.

FIG. 10 shows the pulsed second wavelength waveform according to oneembodiment of the current invention.

FIG. 11 shows a 3D map of areas where intensity or heart rate increaseis associated with either different electrode locations or differentpower/wavelength forms provided to a patient that isolates and locatesthe particular area of inefficiency.

FIG. 12 shows a basic representation of how a factor from each criteriain Table 2 can be created for consideration in developing a standardizedform for measuring, tracking, determining, and improving muscleefficiency.

FIG. 13 shows an individualized wave pattern showing that the pulses canbe varied until the body and brain recognizes each pulse as a naturalaction potential.

FIG. 14 shows the physiological form of a contracted bicep during theinitial motion of throwing a dart which provides the setting forembodiments of the current invention.

FIG. 15A shows a normal frequency change of an action potential during a30 second squat exercise.

FIG. 15B shows additionally an addition of a static frequency that isknown in the prior art.

FIG. 15C shows additionally a representation of how on/off switch canintersect with the proper frequency more often than once.

FIG. 15D shows an embodiment of the current invention that tries tomatch the proper frequency and the frequency changes with the naturalfrequency changes that results in higher yields of making muscle moreefficient.

FIG. 16 shows a leg wrap and electrode system in accordance with anotherembodiment of the current invention.

FIG. 17 shows the outer box of the Neubie, that discloses the system ofthe enclosed invention.

FIG. 18 shows the internal components of the Neubie, which disclosesmusical components geared to produce clean frequencies in the frequencyrange of 0 to 1000 hz.

FIG. 19 shows the circuit board drawing of the electrode components thatis capable of producing the multiple currents needed to disclose thesystem and methods of the current inventions.

The accompanying drawings are not intended to be drawn to scale. In thedrawings, each identical or nearly identical component that isillustrated in various figures is represented by a like numeral. Forpurposes of clarity, not every component may be labeled in everydrawing.

DETAILED DESCRIPTION OF PREFERRED EMBODIMENTS Introduction

Preferred embodiments of the present invention are directed toward amethod of using multiple, direct electrical currents to mimic the actionpotential of a nerve by first using at least one set of direct currentelectrical currents in the range of sound frequencies to synchronize thefrequency and voltage with the body and then providing another one ortwo set of direct currents that are in the wave shape of an actionpotential either in direct mV measurements or in a similar waveformpattern depending on the individual or subject, and then creating abaseline from the measurement of either the changes in heart rate,breathing rate, blood pressure, blood oxygen saturation, galvanic skinresponses, or pain/discomfort levels which allows for the creation of anefficiency standard for which a muscle can be measured for efficiency.

Further, embodiments of the current invention use the reproduced actionpotentials in a frequency that would match the natural body's changingfrequency in stationary positions or during specific exercises thatenhance the bridge between the brain and “inefficient” muscle.

In accordance with preferred embodiments of the current disclosed systemand methods, there is provided a method of delivering specificelectrical currents having waveforms that more closely approximate theshape of the action potential of the human and animal nervous system.Sound that is perceptible by humans has frequencies from about 20 Hz to20,000 Hz. With various electrodes placed on specific muscles and thedistribution of multiple electrical waves with sound wave frequencies,the use of a first sound wave syncs, or harmonizes with parts of thebody, such as the water and fats and epidermis, to reduce the impedanceor resistance of those tissues. The use of a second sound wave isperformed in pulses that reaches and stimulates the nervous system andallows the brain to recognize the natural, more efficient usage of themuscle as its natural state. In doing so, these pulses bridge thebrain's control of the muscles, re-establishing a connection that allowsfor more efficient usage of these muscles. By performing specifictraining exercises and specific movements, it is possible to acceleratethe bridging process to re-engage the body's muscles more efficiently. Athird sound wave can be used to create the dip or other parts of theaction potential when synchronized with the second sound wave electricalcurrent, it can (also??) produce the mirror image of an actionpotential.

In accordance with embodiments of the current invention, FIG. 9 showshow electrodes and movements can be combined towards achieving a muscleefficiency standard or better improving the muscle efficiency by showingan individual 901 throwing a dart 902 with the arm 912 almost in theextended position. In other words, if this arm 912 was in motion, thepicture in FIG. 9 shows an arm that is almost at the release of the dart902. In this particular example, there is a biceps 906 and a triceps907. The understanding that these are antagonist muscles is essential inshowing muscle efficiency. Because there typically is discomfortassociated with the delivery of the multiple electrical currents whereinat least one current harmonizes with the body using sound wavefrequencies and a pulsed frequency that mimics a natural actionpotential, the level of discomfort experienced can be used to helpquantify the degree of muscular inefficiency.

These action potentials can be individualized so that they perform onvarious animals. Although nature respects the waveform of the actionpotential, obvious differences between humans and animals allow us torecreate the differences in these second frequency to match the animalin particular. The closer the match between the wave form and theorganism's innate action potential, the higher the success of rebridgingthe gap between the brain and muscle. In FIG. 9, system 903 deliversthat multiple frequencies of direct current through electrodes 904 and905. The multiple frequencies allow one set to harmonize with the body(which can be conceived as penetrating the outside body and organs) andanother set to mimic that action potential of a healthy or even highlyactive nerve. This electrical current can be applied to different areasof the muscles, and in this example there are many electrodes at 907,908, 909, 910, and 911.

There are a number of ways to calculate the inefficiency of muscles.Again, the inefficiency of muscles for purposes of this patent isdefined as a reduced ability of the brain to connect with the designatedmuscle, resulting in a deficiency in the ability to normally send anaction potential to the muscle. The inefficiency can be measured in manyways, but there is a preferred way. Table 2 shows the different waysthat the inefficiency standard can be measured. (Currently, there are noother known ways to measure the inability of the brain to associate withmuscles in a standardized way that reflects the inefficiency of itsnormal action potential).

A. Qualitative Muscle Function and Performance

Muscle extension, known as eccentric contraction, is vital for efficientmovement in most settings—particularly for high levels of athleticperformance and fitness, and also for many movements of daily life.Modern research shows clearly that proper muscle efficiency allows foreccentric muscle contractions to absorb the forces encountered duringbodily movement, thus protecting more passive bodily structures fromhaving to handle that force. When force is not properly handled by themuscles, the body has to rely on the secondary, passive supports ofligaments, bone, and other connective tissues. These structures aresensitive to mechanical perturbations. They can become damaged, or caneven respond by alerting the body to the possibility of damage. Thissignal causes the body to change its use of muscles in the area, whichcan reduce muscle responsiveness and efficiency, impair performance, andincrease the risk of injuries in subsequent activities.

Unlike the U.S. Pat. No. 5,107,835, the current usage of thesefrequencies can become individualized and specialized based on theparticular movement which unexpectedly heightens the efficiency of thesetechniques that that were well known in the industry to contractmuscles. Although U.S. Pat. No. 5,107,835 got much of the science wrong,the current invention relates in that the proper distribution of properelectrical waves with sound wave frequencies results in a fasterrestoration of muscle efficiency. The current research focuses on thetrue nature of these interactions, and the results show that theirreactivation is not due to them contracting the muscles or re-triggeringthe muscles back to a state of full recovery, but more that these pulsedcurrents properly trigger neuronal feedback that allows the bridging ofthe brain's own control of these muscles.

Clinical evidence now shows that there are more effective means by whichthese various electrical waves with sound wave frequencies can be usedin treatments or training sessions. In the first embodiment of thecurrent invention, there is a method of increasing the efficiency ofmuscles comprising the application of a first and second of electricalcurrents to a muscle wherein the first and second electrical currentsare direct currents in the frequency of sound waves between 20 hz and20,000 hz and where higher levels of muscle efficiency is achieved. U.S.Pat. No. 5,107,835 discloses a similar type of machine where there is anapplication of multiple electrical currents for the stimulation of themuscles, but the current invention relates to the proper means by whichto use such a device to actually increase the efficiency of muscles. Todo so, there must be specific application of proper electrodes toparticular set of muscles and a way of creating a baseline so thatmuscle efficiencies can be measured.

For example, in performing a squat movement, the quadriceps muscles haveto lengthen to absorb force and keep that force out of the knee and hipjoints. Placing electrodes on the vastus medialis and vastus lateralis,and applying a signal of appropriate frequency and power, can facilitatethose muscles' ability to eccentrically contract, resulting in a moreefficient squatting movement. In addition to helping to protect againstinjury, this approach can also prepare the quadriceps muscles tocontract more powerfully in the second half of the movement (moving upfrom the bottom of the squat), which leads to greater strength and speedof movement.

In a simplified look at the action of throwing a dart, the main actionis that of elbow extension. The triceps muscles provide the majorimpulse for this action, while the biceps muscles provide a force in theopposite direction that could resist the elbow extension. In order forthe extension to happen smoothly, the biceps must lengthen, oreccentrically contract, at the same time and at the same velocity as thetriceps shortens. If the bicep were to resist, it could interrupt thismovement, which could reduce the smoothness and precision of themovement, cause force to transfer into the elbow joint and increase therisk of injury, or stop the movement altogether. It would also causeenergy to be wasted in the process, as the triceps have to exert extraenergy to overcome the resistance of the biceps. The electrical signalcan be used to stimulate the biceps to lengthen, so that they do notresist this movement.

This process is exemplified in FIG. 14 which shows the contractedposition of the arm prior to throwing of the dart. Electrodesexemplified by 1408 and 1409 show the different possible areas ofprecise placements in the throwing of dart 1402.

The first and second electrical currents are applied to the muscle witha predetermined level of power and direction of negative and positivepolarity individually of the first and second electrical currents. Incases where the brain is ineffectively stimulating a muscle, the currentinvention calls this “reduced muscle efficiency” or “muscleinefficiency.” For example, muscles can be grouped into agonist andantagonist muscles. If the quads are the dominant muscles, then theunderside hamstrings are its opposing non-dominant muscles. In manypeople, the lessened use of hamstrings over time results in the brainnot having a bridge to connect to the hamstring. The comparison of thedominant muscle and the non-dominant muscle efficiency can be made inaccordance to criteria in Table 2.

Although the application of these electrical waves of sound wavefrequencies produce pulsed contractions with the muscles, the power atwhich the electrical waves are provided can produce strongercontractions in less efficient muscles. The stronger the contraction,the less efficient the muscle is, or in other words, the less it isbridged to the brain and the less it can be effectively stimulated towork to absorb force and protect the body's joints. During training ofagonist muscles, the bridge to the antagonist muscles (if it is nottrained as well) will by comparison be smaller. In injuries, the effectson muscles surrounding the injury result in inefficient connection tothe brain. The level of efficiency may also vary by individual (by theirweight, age, gender, hydration level, training status, and many otherfactors). But what is consistent is that one individual tends tomaintain the same level of efficiency, and thus one individual'sprogress can be measured by comparing data from different dates.

Example 1

There is a threshold of power which all humans can achieve beforecomplete immobilization. If that number is set at 100, we can call itthe Maximum Threshold Level (“MTL”). There is also a maximum level ofdiscomfort felt by an individual, and that number can also be designatedfor each individual and set depending on the particular client. Forexample, if Client A is given the electrical sound wave currentsprogressing from 0 to higher power, the level at which the Client Astates “STOP” or if there is conventional device for Client A to stopthe process when maximum pain is felt (e.g., conventional stop buttonsknown in treadmills is used) that number can be expressed as MaximumPain Level (“MPL”). Each patient can have a ratio of MPL/MTL at adiagnostic phase of Client A. Thus, on subsequent visits, this MPL/MTLcan be compared. If Client A stops the process of power at 20, Client Awill have an MPL/MTL ratio of 20/100 or 0.2. On subsequent visits, ifClient A is able to achieve 40, than his ratio increases to 40/100 or0.4. The MTL would be different in each individual for this particularembodiment because the MTL would be set during an initial diagnostictesting of Client A.

If a ratio is needed that tests against a standard, there can beincorporated two other variables. MMTL is the Maximum Machine ThresholdLevel, wherein ratios can be made and compared to a constant that allowscomparisons of different individuals to an absolute scale. Trackingprogress of each individual by comparing his thresholds with statisticaldata when compared to a maximum machine level allows for the tracking ofstatistical variations of different individuals and tracking theirmuscle efficiency by grouping other factors, like weight, age, gender,height, hydration level.

Another variable includes the Minimum Inefficiency Level (“MIL), whichis the level at which Client A notices the inefficient bridging betweenthe brain and the muscles. This can manifest as subjective discomfort, afeeling of tension as if one has to “fight against” the machine, orbeing visibly shifted or moved out of position by protective muscularcontractions. By using MIL with other variables like MMTL and MPL andMTL, various statistical ratios can be created for the use ofstatistical studies that are quantitative. At best, prior art has onlytried to qualitatively measure “cellular disruptions.”

In one of the embodiments of the current invention, what is disclosed isa way to measure muscle inefficiency wherein “muscle inefficiency” isdefined by the reduced ability of the brain to bridge electricalcommunications to particular muscles that allows the muscles to properlycontract and relax. In other words, there is disclosed a measure, orscore, or a quantitative, unit-based system wherein one person cancommunicate the physiological efficiency of a muscle to another personand where the other person would have a quantitative understanding ofthe muscle condition and its efficiency. In doing so, such measurementscan lead to a quantitative understanding of the progress during orthroughout different treatment periods.

By using different parameters, a study of the disclosed electricalcurrents can provide an accurate score of muscle efficiency. This can becalled a Neuroscore. A Neuroscore can let people know what level ofefficiency a particular muscle has, much like the blood pressure is aquantitative measurement of pressure exerted by circulating blood uponthe walls of blood vessels which is expressed in terms of the systolic(maximum) pressure over diastolic (minimum) pressure and is measured inmillimeters of mercury (mm Hg). Norms of healthy and unhealthy bloodpressure are well understood in the medical community. With the presentinvention, norms of elite, average, and poor muscle efficiency can besimilarly understood within the medical, physical therapy, sportstraining, and similar communities. The Neuroscore is a measurement ofmuscle inefficiency. In one embodiment, the Neuroscore is measured by[MPL]×[frequency]×[power]×amplitude×Y where Y is the average heart rateor heart rate variability over a certain time period, such as oneminute.

In another embodiment the Neuroscore is measured by using average heartrate or heart rate variability over 1 minute+the number of breaths in 1minute while on a certain level of the machine. The certain level can bethe MPL or MMTL or MIL. Such Neuroscore can be scaled from a 0 to 3scale using conventional ratios. Such Neuroscore can alternatively bescaled to a 0 to 100 unitary measurement system having proportionalmeasurements.

The specific location of the electrode placement can be stored by usingconventional grids. For example, the quads of the leg can be broken downinto an XY coordinates axis as in FIG. 16, and by doing so, there can bea specific location description of the electrode's placement. By doingso, another factor of specific electrode placement can be used in thefactor of a Neuroscore. For example, the difference in heart rate over aminute period of time having the electrode in A1 position as opposed toa D4 position would map muscle inefficiency individually for thedifferent locations. Heart rate is simply an objective measurement ofexertion by the subject. So when the electrical currents run through anarea where the muscles are inefficient, the subject experiences moreexertion because the lack of communication between the brain and musclecauses the protective responses with associated discomfort experiencedby the patient. These responses are neurological, and will also affectother aspects of the body that are neurologically controlled, like heartrate. Over a certain period of time, Client A can be measured in heartrate or heart rate variability while the electrodes are placed in onearea or another. This provides a quantitative basis by which aNeuroscore can provide a score showing muscle inefficiency.

The Neuroscore of each muscle may be different, because the level ofamplitude and frequency that is needed to stimulate an efficiencyresponse will likely be different in each muscle. In other words, whenthe Neuroscore is calculated for the quads and hamstrings, each may havea different baseline of electrical current parameters. Thus, each musclemay have a different Neuroscore. In one embodiment, Client A can saythat his Quad Neuroscore is 45.5 and his Pectoral Neuroscore is 50. Eachof these Neuroscores will be based on its own respective criteriaincluding heart rate or other objective physiological measurement, MPLor MMTL or MIL, and whatever factors best enable the formula to measuremuscle efficiency.

One of the best benefits from a score system is the ability to trackprogress or track parameters for statistical studies on success. Successcan be measured by the change of inefficient muscles to levels ofgreater efficiency. That change can be quantified as the delta inNeuroscore over a certain time period. Studies have shown that types ofalgorithms needed for each and every muscle is different. For example,the Quads can produce a variety of heartrate from 90 to 160 in a 40 yearold male, but the variation of heart rate for that same 40 year old malein the calves is 85 to 130. The differences are mostly due to the sizeof the muscle and the density of nerve concentration. Muscles thatrequire greater precision for finer movement have a higher density ofnerves for greater control, whereas muscles that perform more grossmovement have fewer nerves. The same machine output can deliver adiffering amount of current because of the density of nerveconcentration. Also, stimulating a larger muscle will create a greaterdemand for energy than a smaller muscle, and will tend to have a largereffect on heart rate. Thus, the formula can compensate by allowing adifferent method of Neuroscore calculation for the Quads and a differentone for the Calves, each having a different formula incorporatingdifferent ranges of heart rate. Other factors like MPL, MMTL, or MIL arealso different for each muscle group. The current invention, however,uses a novel form of these parameters in measuring muscle efficiency.

In an embodiment of the current invention, there is conceived aconventional microprocessor, memory, input means, export means, outputdevice (like a screen) and power source to store individual clientlevels of information including gender, weight, height, age, body fat,heart rate, and other physical parameters. It also allows for theprocessing of MPL and MTL information, its ratio and other ratios. Thereis also a LFS (“LEVEL OF FIRST SENSATION”) that can be used as a factor.Such ratios can be used to build a chart of progress or even graphs ofprogress to Client A. Such information can be studied as to what linkscan be made between various health parameters and muscle efficiency.

Client level information and ratios stored in the client informationdata can be changed or progressively tracked using conventional ways todatabase client information, not excluding conventional database SQLtechniques. Client information can be compared in past methods whereinfurther progress is stored and new ratios of levels of maximum levels ofdiscomfort is compared to baseline.

The use of this invention's particular ability to individualize thefrequency of the reproduced action potential allows the rebridging ofthe brain to inefficient muscles by mimicking the actual neuron actionpotential. This heightens the level of “awareness” the brain has ofthese areas of inefficiency, and when combined with exercises thatcontract these muscles, the bridge to the brain is reconnected muchfaster. In many case, there is 20-50% improvement in efficiency just inthe first application of the device. In over 500 patients that wereapplied this wave with movement techniques that coincided with thecontraction of that muscle, there was immediate response and increasedefficiency in the muscle in over 90% of the cases. And when combinedwith specific movements, such as lunges or squats with the applicationof electrodes in working muscles during those exercises, there wasimproved MPL/MTL in every case.

B. Electrical Stimulation: Components, Electronics, Techniques, andParameters

Example 2

In FIG. 9, electrodes 907, 908, 909, 910, and 911 comprise a network ofelectrodes that are carefully placed on various parts of the muscles. Bysending the multiple electrical currents of sound waves wherein thepulse of the second wave syncs with the nerve's action potential, avarying level of intensity are felt by the patient. The patient canprovide feedback to the technician verbally as to which feels stronger(much like optometrist asks which lens allows a patient receivingcorrective lenses to see letters more clearly). The patient can alsoprovide feedback in relative portions saying in a scale of 1 to 10 howmuch pain is felt. Ideally, box 903 will measure the relative discomfortfelt at each location on the array of electrodes and store/process thatinformation to aid in finding the areas of muscle inefficiency. Usingconventional recording systems, such as a microprocessor, memory, amotherboard, RAM, basic firmware, such parameters of pain or discomfortthresholds can be measured and recorded. In objective parameters,discomfort is associated with increase in heart rate, or decrease inheart rate variability, or increase in perspiration (or breathing rate,or blood pressure, or a decrease in oxygen saturation rate, or galvanicskin responses which increases surface electrical conductivity asperspiration increases) during higher levels of discomfort. In otherwords, if the muscles are inefficient, the body will respond with“protective mechanisms” that include perceptions of discomfort, whichwill increase the heart rate, blood pressure, breathing rate, andincrease the level of perspiration. If this is measured using a computerprocessor over a long period of time, e.g., 5 minutes, or 10 minutes, or20 minutes, or 1 hour, or 4 hours, or 24 hours, or longer, there can bea consistent mapping of the heart rate associated with the muscleinefficiency. In other words, let's say that electrode 907 is turned onand the recipient experiences a subjective 5 out of 10 discomfort. Ifstimulation through that electrode 907 is continued, there will be anincrease in heart rate associated with the inefficiency of that muscle.The more inefficient the muscle, the higher the heart rate. The higherthe power, the higher the heart rate. So, if we maintain the same powerand current and provide the pulsed second frequency, there will be anincrease in the heart rate over time, such as 30 seconds, or 2 minutes,or 5 minutes. If electrode 907 is then turned off and electrode 908 isturned on at a different area of the muscle, and if the patient thenexperiences discomfort on a subjective level that is 7 out of 10, thenthe technician can isolate the location of the muscle inefficiency. Inaddition, because of the higher level of subjective discomfort, there islikely to be a natural higher level of heart rate and higher level ofperspiration. If the level of perspiration can be measured using asimple circuit and if a standard heart rate monitor is used inconjunction with the different electrodes being turned on and off, therecan be a precise mapping of the muscle areas that experience higherlevels of inefficiency, and a way to objectively quantify informationthat would otherwise be very subjective and difficult to track.

Box 903 will also have conventional means to measure heart rate, heartrate variability, blood pressure, blood oxygen saturation level, skinconductivity, and/or breathing rate. For purposes of identifying“matches” these levels can be measured manually. “Matches” means theability for the pulse frequency to match natural action potentialfrequency. The depolarization of a neuron caused by the stimulus abovethe threshold voltage results in a complete action potential (i.e., itis all-or-nothing). If the stimulus strength is increased, the size ofthe action potential does not get larger. The size (i.e., amplitude) ofthe action potential of a given animal is generally the same andindependent of the size of the stimulus, but small variations existbetween different animals. The nervous system creates stronger muscleresponses by increasing the frequency of the action potentials. Thus,the stronger the stimulus, the higher the frequency at which actionpotentials are generated. Therefore, the frequency of action potentialsis directly related to the intensity of the stimulus. However, asdescribed in prior art references like U.S. Pat. Nos. 5,107,835 and5,109,848, which was published in 1992 or U.S. Patent Application No.20130060304 A1, there has never been any attempt to match the changingfrequency during the application of the direct currents. It is shownthat increasing and varying the frequency (in a diagnostic process) cansuddenly find the optimal frequency at which the body recognizes as“normal.” In other words, during the exercise of a certain musclemovement, the frequency of the muscle will increase relative to theneeded exertion of the muscle. The current invention challengestraditional notions of “cellular disruption” and tries to find the“sweet spot” of frequency that best matches the actual frequency thebody would produce if the muscle were behaving efficiently.

All the examples used in the disclosure use the multiple frequenciedmachines, but there are more than one way to put together a machine thatcan produce one set of electrical currents (direct current) at a soundfrequency level of 20 hz to 20,000 hz and then another pulsed set adifferent rate, the difference in the level should be equal to or higherthan the action potential reaches of range. For example, in a neuron ofa human, −70 millivolts (mV) is the peak and the threshold potential isaround −55 mV. The membrane potential abruptly shoots upward, oftenreaching as high as +100 mV. So, the range is around 170 millivolts. Thefrequencies for both the resonating and the pulse must accommodate forthe range in voltage patterns.

In U.S. Patent Application 20130060304 A1 titled “Method and Apparatusfor Generating Electrotherapeutic or Electrodiagnostic Waveforms” thereare clear methods of providing multiple frequencies and ones within therange of sound frequencies. This application has a FIG. 6 within itsdisclosure that teaches the disclosure of patterns that even resemblerefractory sections, but there is no disclosure that the motives are tomimic the action potentials, and the current invention also disclosesthe ability to separate the two sets of frequencies so that one syncswith the body and the other syncs with the nerves in a manner thatpulses signals are identified by patients as nerve action potentialsignals. Doing so has resulted in immediate accelerations of healing andgains in performance. In 100 patients studied, 99 feel immediateimprovement in muscle activation, manifesting as force being absorbedback on the muscles that were inefficient beforehand and a sense ofgreater ease or less pressure in the relevant joints. In training, theresults show over 65% improvement when compared to conventional weightlifting or nautilus-style gym equipment training. In therapy, thereactivation of muscles to take on their force absorption role allowsthem to naturally protect an injured area while it heals, resulting inover 60% faster healing times.

In animals, the location of injuries has been identified by use ofelectrode placements and mapping of heart rate increases in over sixdifferent muscle groups. In each of these cases, there were increasedmobility in the injured areas at an improvement of over 50% compared toconventional means of casting and other forms of immobilization of thejoints and muscles. There are direct evidence supporting concepts thatthe action potential and ability of the brain to sync with the actionpotential of the muscle is required for the body to properly heal ormake the muscles more efficient. Once the muscles are more efficient,the body naturally addresses any injured joints and ligaments, whereasin immobilization or casting techniques the healing process is prolongedand cannot complete until much later when the body is able to re-engagethe muscles. Theoretically, even in the case of a broken bone, if themuscles around the broken bone are fully engaged, it can absorb a largefraction of the forces that bone supports, and doing so may in somecases actually allow the bone to heal faster than traditional methodsinvolving casting.

In FIG. 9, the box 903 shows a device which may comprise a medical ortherapeutic device, according to an invention that identifiesinefficiency in muscles and that heals inefficiency in muscles. Box 903provides a waveform to a patient according to any of the embodiments inthe current invention. The waveform may be generated based, at least inpart, on a digital signal downloaded from the Internet via Internetconnection or downloaded from another source via USB port. Such adigital signal may comprise an electronic file that includescomputer-readable code representative of one or more waveforms.

A waveform may attain any of a number of shapes. For example, a waveformmay comprise a sinusoid, a square wave, a sawtooth wave, alow-duty-cycle pulse, microcurrent wave, or an arbitrarily-shaped wave.A waveform may comprise one waveshape (or other parameters) for one timespan, another waveshape (or other parameters) for a subsequent timespan, and so on. Variables of waveforms may include time between pulses,pulse duration, duty cycle, shape of pulses, frequency modulations,amplitude modulations, pulse width modulations, ramping, peak on-times,surging, decay rates, and so on. In the example shown, waveform maycomprise a pulse including two peaks. Such waveforms are merelyexamples, and claimed subject matter is not limited to anyparticularly-shaped wave or signal.

Box 903 may include a screen, which may comprise a touchscreen, forexample. Box 903 may include a number of switches, knobs, or keyboard toallow a user to manipulate the device, input patient information, adjustparameters of a waveform, and so on, for example. A waveform fileexecutable by device may include instructions regarding sensitivity orfunctionality of any of switches, knobs, or keyboard, for example. Suchinstructions may also be executable by device to operate the screen withparticular features or have particular functionalities.

A waveform may be described by any of a number of techniques. Forexample, one or more mathematical equations may describe, at least inpart, a waveform (e.g., amplitude multiplied by a cosine function havinga particular frequency, or a series of sinusoidal functions respectivelyhaving varying frequencies or amplitudes). In another example, a tableof values may describe a waveform. Such a table may include waveamplitude as a function of elapsed time of a cycle of the waveform

In U.S. Patent App. No. 20130060304 A1, there is a disclosed a “waveformcode” comprising an exponentially-rising/decaying pulse having afrequency of 500 hertz (Hz) for 2.0 seconds, theexponentially-rising/decaying pulse having a frequency of 800 hertz (Hz)for 10.0 seconds, the exponentially-rising/decaying pulse returning to afrequency of 500 hertz (Hz) for 2.0 seconds, which repeats. Conventionalpieces of electronic components can be added to make both frequencies.First, there has to be a direct current converter and a splitter or anability to have two sources of direct current.

With the ability for the device to generate different waveforms havingdifferent shapes, magnitudes, and frequencies (for purposes ofdescribing a machine that can alter the waveform patterns, U.S. PatentApplication No. 20130060304 A1 is hereby included within thisdisclosure).

Where U.S. Patent Application No. 20130060304 A1 falls short is thefollowing:

Harmonizing the first set and second set of frequencies such that thefirst set syncs with the body (outer epidermis, bones, fat) and a secondpulsed set that resonates with the nerve and has the ability to mimicthe action potential. U.S. Patent Application No. 20130060304 A1 doesnot try to achieve the mimic of the action potential. Because thereexists the ability to quantify muscle inefficiency using the techniquesof this invention, there is the ability to alter the pulse delays orpatterns or heights so that the increase in heart rate or increase insubjective discomfort levels can be associated with better resonatingmatches of the action potential. The level of achieving the harmony withthe natural action potential from U.S. Patent Application No.20130060304 A1 is not achieved or may be intermittently coincidental,but the current invention enables an isolation of the muscles that areinefficient and it also enables a standardization of muscle inefficiencyso that the second frequency can better mimic the natural actionpotential of the selected nerve that is attached to the selected muscle.Even over U.S. Patent Application No. 20130060304 A1, improvements inmatching the action potential signal has resulted in surprisingly over23% better efficiencies in over 60 patients studied when compared tocontrol patients. This is due to scientific understanding that when thefrequencies actually match patterns of action potentials that aregenerated naturally during specific body movements, the brain is“rebridging” the connection between the brain and the muscle, whichnormally exist in more efficient muscles;

U.S. Patent Application No. 20130060304 A1 does not disclose theisolation of muscles using subjective input or objective input (e.g.,heart rate average increase over 2 minute intervals) by using differentelectrodes or different electrode locations and then determining theintensity and then creating an array map. For example, in FIG. 16, thearray of a mapped out area is shown that covers the quad area of theleg. Bendable areas 1603 and 1606 allow the leg wrap to bend and kneehole 1607 allow the leg to move and breathe. The electrodes in 1601,1602, 1604, 1605, and 1608 can be calibrated with a technician or acomputer to take in the levels of intensity that can be measured bysubjective or objective standards described in Table 2 above. In thecase of subjective input, the level of intensity can be measured by grippressure or verbal expression on a scale of 1 to 10. In the case ofobjective input, a longer area can be spanned using multiple electrodesor careful location selection of the electrode and placement on a muscleso that an increase in heart rate or change in other physiologicalparameter can be associated with a more injured muscle or a moreinefficient muscle. Because there is a basis to standardize the muscleinefficiency based on this disclosure, there is a manner to create a mapshowing precisely what part of the muscle needs work. Because of theprecision of this method, in over 500 patients studied, the improvementsin isolating and addressing muscle inefficiency is enhanced by over 40%compared to the traditional methods, such as used in disclosed in U.S.Pat. Nos. 5,107,835 and 5,109,848, which was published in 1992 or U.S.Patent Application No. 20130060304 A1. The references of U.S. Pat. Nos.5,107,835 and 5,109,848 show ways that multiple frequencies can be addedin a direct current having pulsed patterns in the second frequency, andbecause these references also disclose traditional methods of creatingthese direct current frequencies, these references that are now in thepublic domain are included herein for their reference and disclosure ofthese frequencies. In FIG. 11, high level 1103 is associated either withsubjective input from patients showing high level of intensity ordiscomfort or in the objective input from higher heart rate averagesover a longer period of testing time.

U.S. Patent Application No. 20130060304 A1 does not actually mimic theaction potential, but the current invention uses the same range coverageof nearly 150 mV that an actual potential range covers. These referencesare all about trying to trigger the action potential. If the machinetriggers the action potential with a pulse, then the application in U.S.Patent Application No. 20130060304 has done its job. Unlike these priorart references, the current invention mimics the action potential sothat the brain recognizes the pattern. It does not need to actuallytrigger an action potential, as the appropriate biological adaptationswill occur as long as an action potential signal is received by thebrain. When combined with exercises or movements that normally dotrigger these action potentials, then the ability exists to rebridge thebrain's connection to the under active muscles. The current inventionmimics the actual number of mV by reversing the wave form of directcurrent such that it produces the negative 90 mV necessary to mimic therefractory period of a real action potential. No other disclosure doesthis, and by comparison, the mimicking of an actual action potential hasresulted in even faster rates of recovery with up to 80% improvementover these prior art techniques.

Up to now, there has not been a standardized method to determine muscleefficiency. Although almost any person can subjectively determine when amuscle feels weak or when a muscle is not working right, doctors ortechnicians currently have no parameters to objectively determine muscleefficiency. In other words, doctors cannot communicate with each otherthe level of disconnection between the brain and the muscles, which inmany cases is the reason why a subject feels pain (especially when forcethat should be absorbed in muscles is transferred to joints andligaments). By using objective measures, such as heart rate average, orsubjective measures, a system of comparing that threshold number witheither its antagonist muscle, or opposite body muscle, or previoussessions, or values of other users in a database, can determine thehealth of that muscle. For example, in a thoroughbred horse that has hada full diagnostic, baseline reading with average heart rate measures ata certain power of the box 903 and application of the action potentialmimicking frequency, if the thoroughbred horse has an injury such thatrunning another diagnostic increases the heart rate at certain electrodelocations, a technician may be able to isolate the actual injury withouthaving to “read” the horse or take any x-rays or MRI images of thehorse. Further stimulation of those muscles found to be affected willmimic the actual action potential and re-engage those recentlydisengaged muscles. This stimulation will repair the bridge between thebrain and those muscles, and, surprisingly, this approach leads toincreases muscle efficiency that are over 35% greater in human andanimal subjects than can be achieved with conventional stimulationdevices, including devices disclosed in U.S. Pat. Nos. 5,107,835 and5,109,848, which was published in 1992 or U.S. Patent Application No.20130060304 A1. Table 2 of the current invention shows differentpermutation capabilities for determining a numerical value. One can useone or more items from each Criteria to derive a standardized formulafor muscle efficiency. Because there has been no effort made in thisfield, the current invention leaves open the possibilities of usingthese or other derivative methods to come up with a standardized methodsof muscle efficiency. As an example, in FIG. 12 takes into consideration“Objective: heart rate increase over period of time and address theincrease in heart rate over different areas of application” of Criteria1 in Table 2. It then takes “Measured agonist/antagonist muscle” elementof Criteria 2 in Table 2. It then takes “Ratio of Heart Rate variables”of Criteria 3 in Table 2. It then finally takes into consideration “VaryCurrent (or power)” of Criteria 4 in Table 2. Using these criteria, FIG.12 shows how a standardized form of muscle inefficiency can bedetermined. In combining these, a new index can be formed that takesinto consideration each of these four criteria. What is important isthat there is a means by which a standardized form of measuring muscleinefficiency can be achieved—objective input and subjective inputconsiderations are taken into consideration.

A further distinction is the useful manner in which a sync with anaction potential can provide unique training and healing methods that,when applied to certain movements or exercises, creates a furtherenhancement of the brain's ability to re-bridge its connection to thesemuscles. Thus, the application of these specific frequencies whencombined with unique techniques can provide drastic improvements inmuscle efficiency. In over 500 patients studied, mobility increased 95%faster using these techniques than with traditional physical therapy. Inthese same patients, over 15 surgeries were avoided based on the abilityof the brain to re-engage with these muscles. Methods are describedbelow.

It is well known in the industry to take into consideration patientinformation such as body weight, age, sex, heart condition, injurystatus, injury/health history, and history of treatment using box 903.But considering the 3D capabilities of being able to precisely isolatemuscles and because there now exists a way to track progress in muscleefficiency based on Table 2 considerations, patient information takes onnew meaning. Patient information can be used as the baseline informationto form an efficiency measure. For example, based on Table 2 criteria, apatient may have an inefficiency index in the biceps of 1.1 one week and1.05 the next week, which for purposes of this example means that thereis an increase in efficiency (less heart rate for the same applicationof power for the same muscles). Such considerations are especiallyhelpful in the context of animals or patients that are unable tocommunicate or locate the pain, and can also be helpful to measuresubtle changes that indicate improvement in function but may not yet beable to be perceived by the patient. In over 15% of the cases of 500patients studied, techniques used in standardized methods of Table 2actually resulted in location of the weakened or inefficient muscle whenother physicians were not able to locate it.

A processor can manipulate the waveform, but the array creation ofdifferent power levels or considerations of this application are novel.Because of the ability to create a 3D map and the ability to standardizemuscle efficiencies, there is potential in individualizing care withalgorithms. After the isolation of the muscle inefficiency in patients,a technician will then have an understanding of where to treat themuscles (precisely) and what parameters to use (e.g., power andisolation of mimicked action potential).

FIG. 10 shows the second wavelength waveform according to one embodimentof the current invention. The pulses resemble action potential shown inFIG. 2, which shows the polarization rise 1004 of the action potentialshape and the depolarization downward shape 1002, and it has arefractory section 1003 and notice that these pulses are sent in orderso that refractory section 1005 is the same. The refractory section 1006has a slight downward path as in the real action potential. In otherconventional systems that use pulses of direct current, none have shownto mimic the action potential. The repeated pulses produce a baseline at1001, which means that to the body, the brain receives continued pulsesof forced action potentials. If the muscle is healthy, the actionpotentials only reproduce the natural pattern of activation of theseaction potentials, and no rise in heart rate is felt when the level ofstimulation matches that of normal activity. If the muscle is nothealthy, or inefficient, the brain has an inability to properly processthese action potentials themselves, which means that the brain resiststhese patterns of action potentials, and creates discomfort or a rise inheart rate or other neurological response, all in its attempt to limitor reduce the activity of the inefficient muscle.

If there is injury or some form of damage in this area, the body thennaturally address these concerns because this signal applied duringtreatment of the effected areas causes the brain to become more aware ofthat area of the body and any repair work that needs to be done there.As a result, in areas that are recently injured, the body will bestimulated to activate the biological processes and send the resourcesnecessary to heal these damaged areas much faster. Even in injuries thatare many years old and have not fully healed, the stagnant healingprocess can be re-engaged and stimulated to move towards completion.

The improvements in muscle efficiency described above provide afoundation for an efficient healing process. As these muscles workproperly, they can form a natural brace or shield around an injured areato protect it against further damage while it is healing. Combining thatfoundation with the acceleration of biological healing processes, thebody has been proven to heal from a wide variety of ailments 30 to 70%faster than with traditional methods.

When training for athletic performance, stimulating diverse areas of thebody with the multiple electrical waves of sound wave frequency evokesthe same natural reaction of the body to make these muscles moreefficient. This effect has been proven to heighten the performance ofthese muscles to enhance overall athletic performance. For example, anathlete performing bench presses or squat jumps can activate thenecessary muscles, at the appropriate time and in the appropriate way,to achieve immediate improvements in muscle output that lay thefoundation for more efficient gains of muscle tone, mass building,flexibility, strength, speed, and power. Often, this is accomplished byan actual enhancement of the nervous system. This type of stimulationcan trigger restructuring of neurological synapses and the preferentialdeposition of myelin to improve the performance of the specific pathwaysthat are stimulated.

C. Quantitative Measurement of Efficiency

By mimicking the action potential, the next stage is actually to performvarious movements that coordinates the general firing of the actionpotentials in a more efficient muscle. In other words, if the muscle wasefficient, the action potential would generally be moving down thenerves, but because of some form of injury of inactivity or misuse,there arises the occasion where the brain does not fire the actionpotentials to these muscles in a normal, general pattern. In these case,the use of a mimic potential can provide the ability to accelerate thebrain's ability to re-engage and bridge the brain's communication to theinefficient muscles. When these inefficient muscles are stimulated witha direct current waveform in the shape of an action potential, theresults show an improvement in over 80% of its patients. And in 100% ofthe patients, there has been a 75% measurement of healing to fullefficiency from other controls.

As shown in Table 1 (Muscle Efficiency Measurements using the actionpotential mimicked patterns):

% % Maintained % Maintained % Maintained % Maintained Improvement inImprovement in Improvements Improvements Improvements Initial Second inThird in Fourth in Fifth Patients Treatment Treatment TreatmentTreatment Treatment 100 Female 90 80 50 70 80 100 Male 90 75 54 77 88100 Female 90 75 60 80 90 (Objective) 100 Male 90 80 60 85 92(Objective)

Table 1 is a measurement of muscle efficiency improvement by methodsused in this disclosure. The treatment of these patients were acombination of the matching of the action potential of the electricaldirect currents in combination with various exercises that wouldnaturally change the frequency of the muscles during the exercise.Muscle efficiency is a term of lexicon used in this application to meanthe ability of the brain to communicate with the muscle in a normalfashion wherein a normal communication between the brain and the muscleallows for the transmission of signals that permit the muscle to extendand contract quickly. The determination of these characteristics in thenatural setting is the ability to send the waveform of the actionpotential in various frequencies to the patients. These measurementswere made using subjective tests and objective tests. The methods usedin combination with the particular individualized delivery of a waveformin the shape of an action potential demonstrate increases in muscleefficiency for both the subjective tests and the objective tests. Inmany ways, the subjective tests can described as so: stimulate thepatient's body with a direct current according to the embodiments of thecurrent invention. Because of the multiple electrical currents at soundfrequency pulses mimic the natural action potential, areas of muscleswherein there is inefficiency (or areas to which the brain has a lessthan normal ability to send proper action potentials) provide discomfortbecause these action potentials are behaving as if the muscles werefully efficient and engaged. By changing the frequency of the electricalcurrent pulses, there is associated match when the discomfort or theobjective tests show the highest results. In other words, with theproper frequencies sent during proper movement of the muscles, therewill be pain or discomfort in proportional measures according to howunder active or inefficient the muscle is. The more inefficient themuscle, the more discomfort from the frequencies of these waves. But upuntil this invention, there had not been any scientific or statisticalways to use this information. And up until this invention, there had notbeen ways to better mimic the action potential such that the feedbackcan provide faster rates of muscle recovery.

Based on the body's reaction to the application of the reproduced actionpotentials at direct currents and the mimicking of the action potentialsusing precise locations and precise movements, a standard can be derivedthat determines muscle efficiency or muscle inefficiency. Because of thevariations that exist between individuals and in muscles, there arevariations on certain criteria that can combined to derive at astandard. Table 2 shows four of those criteria, and according toembodiments of the current invention, any one element in each criteriacan be used to derive a standard for muscle efficiency/inefficiency.According to embodiments of the current invention, one or more criteriacan be used and as many as four or combinations of more than onecriteria to derive a baseline of muscle efficiency such that futuredetermination can be calculated.

TABLE 2 CRITERIA 1 STANDARD (TYPE OF INPUT FOR DETERMINING MUSCLEINEFFICIENCY) Subjective: measurement of discomfort or pain from a scale(like 1 to 10) by different areas and then mapping out the degree ofpain from each area Subjective: asking patient to grip harder or biteharder and record the strength of pressure vs. different areas ofapplication Subjective: User push button asking client first feeling ofpain and moment of intolerable pain, push button may also be a killswitch Objective: heart rate increase over period of time and addressthe increase in heart rate over different areas of applicationObjective: heart rate average over longer periods of time while currentis applied to different areas creating a map of discomfort Objective:use of forced contractions and feedback from contractions (do we need toadd breathing rate, perspiration, blood pressure, etc. here to cover ourbases for other potential criteria for measurement??) CRITERIA 2BASELINE CONSIDERATIONS FOR MUSCLE INEFFICIENCY Measuredagonist/antagonist muscle comparison Muscles can be compared from leftside and right side Muscles can be compared from previous uses andstatistical models showing history Muscles can be compared usingdatabase Muscles can be measured immediately every X seconds and resetsCRITERIA 3 MEASURING FACTORS/DATA Heart Rate Max, Ratio of Heart ratevariables Ratio of Max Discomfort Level to Lowest Level of PaintComparison to Database of Standards Constant Measurements X secondsheart rate Heart Rate Variability CRITERIA 4 HOW TO INDIVIDUALIZE THEREPRODUCED ACTION POTENTIAL TO MIMIC Use Action Potential Shape and getfeedback Use same voltage and frequency range as real Action Potentialand get feedback Vary the frequency during stationary positions forvarious periods of time (1 second to 5 hours) Vary Current (or power)Vary the frequency during exercises wherein the variance of thefrequency match an exponentially rising curve as the real actionpotential during the contraction of the muscle during the movement

Table 2 shows permutations on how to calculate inefficiency in a muscle;by doing so, other methods of muscle inefficiency diagnostic testing isderived, and such can be used to calculate other useful data forpurposes of treating muscle inefficiency. The following are mereexemplary and can be derived from the above information.

The match is determined by subjective or objective results of varyingthe frequency slightly in a 150 mV range and changing the on/off of thepowerful in a pattern that provides electrical current in periodicforms. This does two things: first, by varying the frequency, every timethe frequency matches with the body's actual frequency used in theexercise, there is exertion. This is shown in Table 3 below:

Difference in Subjective frequencies Perspiration Grip pressure used inHeartrate Breathing rate (based Oxygen (precent grip second variabilityrates Blood on Saturation pressure of pulsed (per (times per Pressuregalvanic Rate (% full pressure frequency minute) second) (standard)test) increase) grip) −50 mV 90 23 140/70 10%  0% 15% −25 mV 90 24140/70 10%  0% 25% 0 105 35 160/90 15% 10% 85% 25 mV 105 35 165/96 15%15% 95% 50 mV 95 27 140/75 11%  7% 40% 75 mV 95 25 140/75 11%  5% 30%

Using the objective measure to determine muscle inefficiency has manybenefits. First, because it is using an objective test, the level ofmuscle inefficiency can be measured objectively over a given period oftime without any verbal or subjective input from the patient. If thepatient is unable to speak (autistic, infant, or animal), the rise inheart rate associated with the different patterns of electrodestimulation provides objective measures on exactly the location ofmuscle inefficiency. This muscle inefficiency is not the normalcontraction of muscles that are provided by conventional medicalelectrode devices using alternating current. Instead, these muscleinefficiency stimulations mimic the action potential, causing the brainand nervous system to believe that muscle is actually moving, andresponding to either permit that movement or attempt to “protect”against it. If you provide this application to thoroughbred race horsesor dogs or cats or any veterinarian clinic, the use of a machine thatcan map out the different heart rates using direct current without thecontraction of muscles can slowly but very accurately provide a computeror a technician a map of muscle inefficiency. Combine that with anumerical standard by which a muscle inefficiency can be determined,there is now a new method of determining whether an animal or patient ishurt without any communication. A patient that is in a coma or anelderly patient that is unable to communicate can attach the electrodesand by slowing changing the different levels of electrode stimulation inelectrodes 907, 908, 909, 910, and 911, a technician can now accuratelydetermine the level of muscle inefficiency. Because injuries causemuscle inefficiency, in short, using the standards and techniques inthis disclosure, there is now an objective, diagnostic tool that canmeasure an injury of animal or patient even without any input for thepatient or animal.

Example 3

By tracking improvement in muscle, the determination of muscle levelefficiency and level of healing can be empirically determined (empiricalin the sense that results are objective and can be provenscientifically). Because there is a unique application of multipleelectrical currents that mimic the action potential in this currentinvention, these are not the same as alternating current electrodes thatcontract muscles, and which are available in many hospitals or medicalfacilities. The application of these frequencies do at least two thingsdifferently: one set of frequencies at a sound wave harmonizes orresonates with the body, which is comparable to a sound wave that cantrigger a resonator. While this one set of frequencies do this, anotherpulse set mimics the action potential and sends signals from theassociated muscle. If the muscle is healthy, the sending of anotheraction potential does not provide any discomfort at all to the patient.If the muscle is not healthy and brain is not efficiently engaged withit, than sending an action potential down the line creates a “protect”response and a brain signal which short circuits the connection andprovides a sense of exertion on the muscles (which sometimes is,although not necessarily must be a contraction). Doing this causes theheart rate to go up when the muscle is inefficient, just as it would inresponse to any physiological stressor. And the inefficiency again canbe measured by comparisons to other databases of normal levels or prioruses that determine a baseline of normal or comparisons of other sets ofagonist/antagonist muscles, or comparisons to the same muscles on theopposite side of the body, or baseline comparisons from previous testsessions. What is important is that by using these multiple set offrequencies, a technician can now derive a standard by which muscleefficiency can not only be determined, but also translated easily.

D. Quantitative Results and Data Supporting Invention and AssociatedResearch

Physiologically, action potential frequencies of up to 200-300 persecond (Hz) are routinely observed. Higher frequencies are alsoobserved, but the maximum frequency is ultimately limited by theabsolute refractory period. Because the absolute refractory period is ˜1ms, there is a limit to the highest frequency at which neurons canrespond to strong stimuli. That is to say that the absolute refractoryperiod limits the maximum number of action potentials generated per unittime by the axon. As described previously, the strength of the stimulusmust be very high in order to ensure that the duration of the actionpotential is as short as the duration of the absolute refractory period.A stronger than normal stimulus is required to overcome the relativerefractory period.

Because the absolute refractory period can last between 1-2 ms, themaximum frequency response is 500-1000 s-1 (Hz). According to results ofTable 3 and other clinical data, the level of matching the actual actionpotential frequency with the activity so that the activity wouldnormally produce that frequency produces the highest rate neuronalfeedback response. As shown in Table 3, there is noticeable differencein each of the tests (breathing rate, blood pressure, heartrate,perspiration, and the subjective tests) when the frequency of the secondpulse is varied at 5 minute intervals at slight variations of thefrequency. At 0 and 25 mV, there is noticeable spike in the match. Thismatch is the recognition of the body that the frequency is normally atthat frequency.

During movement, this frequency will change depending on the level ofmuscle needed for the movement. However, there has not been any currentstudies showing the matching of the frequencies with the actionfrequency change of the movements. The current invention shows that byvarying the frequency, there is a noticeable matching that tells thetechnician at which the maximum level of recognition of action potentialby the brain is recognized. And to increase the current, or power, atthat isolated frequency would coordinate with the brain to re-engagethese muscle. When the movements or exercises are timed so that thecontraction of the muscles are timed in intensity with the level ofpower at matching frequencies, then clinical evidence shows significantincreases in over 60% improvement of muscle efficiency.

The second pulse frequency can also be switched on/off in a repeatablepattern (high speed). Although it may not match the same frequency, thelevel of turning on/off allows the body to pass through the naturalfrequency more often considering it passes through the frequency duringeach initiation of the on button.

The reproduction of the action potentials and the reproduction of thevaried frequencies to natural action potentials are considered“matching” for purposes of this disclosure and the reproductions areperformed in a pattern or in a way that such the body recognizes thereproductions as action potentials, wherein in U.S. Pat. Nos. 5,107,835and 5,109,848, which was published in 1992 or U.S. Patent ApplicationNo. 20130060304 A1, the application of the electrical direct currentresulted in only incidental matching of the frequencies with the naturalaction potentials. In contrast, the current invention individualizes theaction potential and fully utilizes the natural action potential bycreating an electronic version of it that the body recognizes as a realaction potential. This in and of itself is an invention. A furtherinvention is the ability to perform movements wherein there is a higherlevel of “matching” or recreating a neuronal response is made when thechanging frequencies match the changing frequencies of the muscle inquestion (wherein scientifically it is understood that the brainbelieves this movement is associated with multiplied reproductions ofthe action potential). Although normally this pattern was not achievablein prior art because the inability of the direct current electricalcurrents to penetrate the outer body and outer epidermis of the body,the current invention allows such capabilities by using twofrequencies—one to sync with the body and another to pulse and mimic thenerve action potential.

This is distinguishable from prior art in that prior understanding ofthe so-called “weakened” muscle were due to the misunderstood conceptsin muscle recovery. The current invention accepts the natural dynamicsof the action potential and uses the ability of each individual toengage with a reproduction of the action potential, and moreimportantly, the current invention allows the ability to standardize theform of defining the level of efficiency based on this understanding andalso allows for a higher level of recovery from isolating the musclesand parameters that allow for the highest match between an individualsubject (whether animal or human) and a reproduction of pulsedelectrical currents specifically aimed at mimicking its respectiveaction potential so that the brain can re-engage and re-activate themuscle.

Currently, there is no way of accurately stating the muscle status otherthan to say “the muscle is weak” or the “muscle is not working” or“muscle is not contracting.” By using the methods in this disclosure, atechnician will be able to provide a numerical or grade value to thelevel of muscle inefficiency. Table 2 provides the permutations of waysto derive that numerical value. For example, the heart rate can bemeasured during stimulation of electrodes 907, 908, 909, 910, and 911,and these measurements may be made over some period of time overdifferent areas of the muscles, and if analogous heart rates weremeasured in a previous session or on the other side of the body or existin database of standards, there can be a ratio on which to base anumerical value. In this case, let's say that the pain threshold atelectrode 910 occurs at 50 mA of current, when on the exact oppositeside of the arm the same threshold occurs at 100 mA. A ratio of thedifference (50) to the highest level (100) can determine the level ofinefficiency in that muscle. A technician can say that the muscleinefficiency ratio is 0.5 (or 50/100) which can provide an actual,precise number of 0.5. This threshold can be determined by eithersubjective or objective input, such as discomfort level from a scale of1 to 10 or the average rise of heart rates in a given longer period oftime.

In the expired U.S. Pat. No. 5,107,835, very specific forms of multiplewave patterns are used, but the current invention shows higher, evenunexpectedly high results, when the waveforms are individualized andthere is a manner to mimic the action potential. The application offrequencies in the expired patent may show success in re-engaging thebrain, but these are incidental considering the frequency of the actualaction potential does not exactly match with the frequency naturallyoccurring. That is because the frequency that is naturally occurring isslightly changing depending on the constant communication between thebrain and the muscle. The current invention shows how one can derive atthat frequency and if not exactly, enough so that performing certainmovements can actually provide the stage by which the application ofvaried frequency used in the machine and with constant feedback from theclient can result in a match between the real action potential frequencyand the body. More importantly, when this is achievable, one can measureit and use it as a standard to determine overall muscle efficiency. Moreimportantly, because the isolation of the frequency and waveformprovides individualized care, those frequencies can be turned on high(current) and with the same amplitude and regression pattern and themimicking of the action potential frequencies, the results inre-engaging the muscles have been unexpectedly high.

Current technology including U.S. Pat. No. 5,107,835 does use variedfrequencies to engage the muscles, but those pulses overload the neuronsto force the action potential, and they do not mimic them. By changingthe pattern of waveform delivery and then creating a baseline from whichthe pulses can be varied in periods (or frequencies) as shown in FIG.14, the body suddenly syncs with the action potential when matched.Studies in over 50 subjects showed greater than 35% improvement ofmuscle efficiency when these particularized wavelengths and frequencieswere matched with action potentials. Even higher results were shown whenthese varied frequencies were increased at a constant rate during thecontraction of the muscle. More than 40% improvement was shown inpatients when movement of contracted muscles were combined with thevaried frequencies of the delivery of reproduced action potentials. Evenhigher results were shown when the movements were performed to anaccelerated level such that failure of the muscle came at an acceleratedpace; and when this was matched with accelerated increases infrequencies in conjunction with the time. For example, the increase infrequencies was varied by 150 mV from beginning to end. The reproductionof the action potentials were given in the multiple frequency format asdescribed in this disclosure. The patient contracted the muscles wherethe electrodes were placed from 0 seconds to 3 minutes. During this 3minutes, the patient went from 0% effort to 100% effort until themuscles went to completion and failure. During this same 3 minutes, theapplication of the frequencies was increased from the low end to over anincrease of 150 mV in the 180 seconds proportionally and in acceleratedform. Both resulted in over 20% improvement in muscle efficiency basedon heart rate variability measures.

The creation of a national database in contemplated within theparticular example and within the context of Table 2, Criteria factor“database standards.” The efficiency standards for each animal maydiffer. And each muscle will differ in muscle efficiency standards. Eachmuscle is different size and has a different purpose. The frequency setfor each neuron and its connection to that muscle is particularized.Although the muscles on the left side of the body can be compared to theright side (a basis for one of the standards in this disclosure) andalthough the muscles can be compared individuals based onagonist/antagonist and from previous sessions (a history that defines abaseline of normal muscle efficiency), the difference between eachindividual and each animal and each muscle group is varied by thedifference in the frequency that is needed for that muscle. Consideringthis variety, national standards for human and for animals would benecessary for the creation of standards on what would be “efficient” andwhat would be “inefficient” and what value of inefficiency that can beplaced on the muscle. For example, the frequency for a human bicep is at80 hz for the second electrical wave pulses. This is based on thestandards of a human and over 500 patients studied as to what frequencytriggered the highest heartrate variability increase. For the dog, thebicep is at 70 hz for the second electrical wave. The exact reasons areunknown as to why the differences occur, but there is consistency toshow a range or a consistent frequency for non-movement and movementbased calculations. A national database can be controlled via standardInternet connections and there can be crowd-sourcing capabilities topool data for creation of standard in the frequencies and techniquesused with frequencies that best result in a match.

The best scientific understanding of this principle credits this successto the potential to better sync with the frequency of the naturalpattern. For example, in throwing a dart, the triceps has to contractand the biceps must extend during the dart throw. FIG. 13 shows awaveform application in accordance with one embodiment of the currentinvention wherein the time between pulses (1301) is varied until each ofthe pulses is recognized as a natural action potential. This occursdifferently in every individual, but the increase in discomfort orobjective measures, like the heart rate, can indicate clearly the variedstate at which the nerves resonate with the second set of frequency. Asa result, individualized waveform patterns can be created and stored forfuture use. Having a matching resonating frequency has shown over 30%increase in muscle efficiency measures in over 500 patients tested.

By isolating the particular location of the muscle inefficiency asdescribed above, and then applying specific currents, the waveformpulses can be increased in frequency (or duty cycle) section 1301.Section 1301 can be milliseconds in variation or it can be actuallyseconds. The pattern of 1302 must be repeatable so that the brainbelieve that each delivery of a pulse is a natural pulse—and in order todo that, the 1301 lengths are varied or increased until optimized. Thevariation can be involved in a diagnostic testing that shows whichvariation best syncs. At some point, the brain will believe that thesignals are actually natural action potentials. Although U.S. PatentApplication No. 20130060304 A1 do carry traits of a peak and aregression pattern that is similar, the incidental application of thesecurrents are not synced with the individual. In one particular example,Patient A used separation of these pulses and variations were tested. Itwas soon discovered through variation of heart rate measures that afurther separation of the pulses was needed, and once pulse spacing waschanged, Patient A was able to achieve higher levels of muscleefficiency rebridging when the power was increased at the samewavelengths. In other words, once the appropriate separation of thewavelength was discovered at a particular location of the muscle, thepower current was increased using that same wavelength that mimics theaction potential. When given in a tempo that is recognized by thenatural body results are accelerated.

When paired with particular techniques of training and therapy, theapplication of these frequencies triggers a natural response in thebrain to re-engage with the muscles to make them more efficient. As oneexample, a patient can perform a proper lunge movement, and with theapplication of the electrodes on very specific areas of the hamstring(located by the processes earlier described), the wavelength pulses canbe varied until there is a response from the brain indicating that thesecond set of frequencies has reproduced an action potential voltagesignal. When this signal is combined with the exercises, it re-engagesthe brain to make these muscles more efficient.

Ideally, in perfectly healthy muscles, there would be no heart rateincrease or discomfort felt even at the maximum level of power appliedto the most sensitive areas of the muscles. Since such elite levels arevery difficult to obtain, there is a need to create a standardizedsystem based on the individuals that can track progress towards thisideal.

Individuals carry different weight, water content, and different levelsof fat. Different levels of electrolytes in the body also affect thelevels of intensity from the stimulation treatments. However, consistentuse of the treatments on one individual can provide valuable data, suchthat if an initial diagnostic is done, later on treatments can becompared to the initial diagnostic baselines so that a ratio ofinefficiency can be made in accordance to the criteria of Table 2.Individuals tend to show a consistent pattern from previous sessions,and deviations from that pattern can provide meaningful insight intowhich variables are affecting their situation.

Example 4

Patient A performs a diagnostic wherein the biceps and the triceps aremeasured. Patient A achieves a maximum output power of 67 on a machinethat has power settings ranging from 0 to 100 wherein 1 is the lowestsetting and, proportionally, 100 is the highest setting, which can be acurrent as high as 200 milliamps. Patient B achieves a maximum of 59.Both of these points are reached by an objective test as described inTable 2, and in this case, the threshold occurs when the heart rateincreases by 30%. In other words, patient A's heart rate increased 30%when the setting was set to 67 for more than 1 minute. In Patient B,that 30% increase happens at a setting of 59. Two weeks later, the samemeasurements are made. Patient A was able reach a level of 74,indicating an improvement in efficiency, either as a response to theprevious test stimulation or something else that affected Patient A inthe interim period. Patient B dropped to 43, and upon investigation, itwas found that he had suffered an arm injury which made his tricepsinefficient. Over 4 weeks, both Patients A and B were able to reachhigher levels, and using their initial 67 and 59 as the baseline, aratio of improvements can be determined. Patient A achieved a consistent84 after 4 weeks, or had an efficiency improvement of 84/67, which is a1.254 index of improvement. Patient B eventually reached a level of 61,even after the initial drop due to injury, which is 61/59, or a 1.034index of improvement (the index would be even higher, of course, ifcalculated from the lower interim value of 43). Patient A was able tostart at a higher efficiency state, and was also able to make a greaterimprovement over his own numbers based on the 1.254 index in comparisonto Patient B's 1.034 index. In this case, the higher index means greaterincreases in muscle efficiency. There can also be ratios that compare apatient's inefficient muscles to the most efficient muscles in that samepatient's body, so that every muscle can have its own index of relativeinefficiency and know how much it needs to “catch up” to work at thesame level as its counterparts. In other words, if Patient A'squadriceps could reach 100, then the bicep's efficiency is now 84% basedon the Maximum Intra-Individual achievable standards. This is an easyway to translate a condition of a muscle to a different user, either onan absolute scale or on an individualized scale for each user.

By utilizing the action potential trigger of the body, various trainingtechniques have been found that when used in conjunction with thefrequencies produce even a higher rate of improvement in making themuscles efficient. Compared to prior art, we have shown that there isunrealized potential using a design that more closely mimics the voltageaction potential occurring in the natural setting. Instead of justputting an injured knee in a cast or brace, this invention candramatically accelerate the healing process for an injury. Performing adiagnostic procedure to precisely find the individual's necessaryelectrode placements and individualized wavelength parameters, andcreating an index to prioritize the greatest muscle inefficiencies, canguide stimulation treatments. Such a process, which is essentially analgorithm, will determine where and how to stimulate the patient toachieve the greatest acceleration in healing and fastest return tofunction. Because of the standardization of the muscle efficiency, a newway of implementing computer technology can be used in the applicationof the frequencies. Currently, there are only vague and oftenscientifically inaccurate discussions of why techniques involving properplacement of the electrodes and use of direct current can improve muscleefficiency. The current invention allows the ability to describe themuscle inefficiency in a manner that is quantitative, and with thatcapability, it allows the understanding that the neuronal-muscularbridging is done best when the action potential of a neuron is mimicked.

There is hardly any research available regarding the efficiency changesto the muscles. When combined with specific exercises or movements, thepulses bridge the brain's connection to the working muscles so that theybecome more efficient even when the machine is no longer being applied.This is because of the application of the pulses, whether it be from twoor three or more electrical currents, allows the brain to recognizepatterns. This process allows the muscle to perform at a higher level,and in many cases it strengthens the muscles at rates faster than whatcan be achieved with merely lifting weights.

For example, during the action of throwing a dart, the muscles of thebiceps 1405 and triceps 1406 work in combination to produce the naturalpower to extend the arm. The biceps must extend and the triceps mustcontract in a coordinated manner. If one set of muscles is lessdeveloped than the other, it often results in the inability of the lessefficient muscles to extend properly, which eventually leads to injuriesof the joints, such as tendinitis. Studies have shown that theapplication of dual frequency electrical currents that are synced withthe actual movement of the arm can aid in the recovery of lost muscleefficiency. For example, if a dart thrower has underdeveloped triceps,then the triceps contraction will be insufficient to promote the actualextension of its opposing muscle, the biceps. By attaching electrodes tothe triceps and timing the exercises such that the current is appliedduring the extension of arm in the throwing movement, the triceps areregulated to contract more efficiently.

Example 5

To do this, there is conceived different phase settings of theapplication of the multiple electrical currents. Phase A settings wouldpromote concentric, overcoming, or positive contraction, and assistmuscles on the lifting phase of a movement. This is done by altering thepower of the second set of electrical current or by altering itsfrequency to harmonize with the action potential signals that triggermuscle contraction. Conventional microprocessors can be programmed toapply the proper Phase A settings during this phase of a movement. Thisphase switching can also be triggered by a mechanical device. Forexample, a sling on an arm that recognizes the extension of the arm canbe attached such depending on the extension of the arm, the applicationof Phase A is delivered to the patient. Because the action potential ofindividual clients varies (especially if other animals are being used assubjects), the technicians applying the electrical currents must havethe ability to slightly alter the wave's amplitudes and frequency (notin shape of waveform).

Phase B settings would be programmed to promote eccentric, yielding,lengthening, negative contraction, and assist muscles on the loweringphase. This is done by varying the flow of current, again changing theamplitudes and frequency to promote the opposite type of contraction. Amechanical device can also trigger the switching from Phase A to PhaseB, such that the machine will work differently to promote differenttypes of muscular contraction.

With experience, research has uncovered a surprising result that whenthe direction of these sound waves are applied in reverse polarity incomparison to the contracting or releasing form of exercise, the abilityto re-engage and bridge the brain to make these attached muscles muchmore efficient allowing these muscles to regain their ability toproperly absorb force. The polarity of the flow can also be matched withthe eccentric, yielding, lengthening, negative contraction such that oneway can be designed to the contraction of the muscle, and the otherpolarity is set on the release of the muscle. This reversal isparticularly valuable when the electrodes are placed on opposing sets ofmuscles, so that the current can be directed towards one set for half ofa bodily movement, and changed to be directed towards the opposite setfor the other half of a movement. According to clinical evidence, it isshown that such matching of variables, such as the polarity and power,during particular exercises results in over 50% higher levels of brainconnectivity and muscle stimulation.

In another embodiment of the invention, settings for Phase A and B canbe matched with muscle efficiency numbers and show precise locations ofmuscle inactivity. The output can also be alternated between Phases Aand B at preset timed settings, such as a setting that automaticallyalternates between Phases A and B at pre-set intervals, i.e. 5 secondslower/5 seconds raising, 10 seconds lowering/1 second raising, 60 secondlowering/60 seconds raising, etc.

Phases A and B are determined by the combination of frequencies andamplitudes that best promote each type of contraction. And because theselevels actually vary by individual, it is necessary for the ability ofthe technician to store the client data of baseline levels so that thetechnician can identify progress or have the ability to spotinefficiencies of muscles.

Phase A and Phase B are different for individual users and are differentfor muscles that are being targeted. Thus, according to anotherembodiment of the invention, there is disclosed a means to storedifferent settings and parameters including power, frequency, amplitudeand waveform of different muscle groups. Conventional LCD screens candisplay “Quads” or “Pectorals” or “Biceps” according to the targetedmuscles. The method includes a system that recalls the various settingsfor each of the targeted muscles. For example, for the Quads, the methodincludes frequency, amplitude, power, and waveform parameters that bestresults in a determination of muscle inefficiency, which can be measuredby subjective determination of patients or objective factors, such asheart rate or heart rate variations over a certain time period, such asa minute. The method also includes the ability to recall those storedsettings for later use. The method also allows for the baseline oftreatments be changed depending on initial diagnostic test ofindividuals because of the variations that exist between individuals.

The underlying mechanisms explaining why these techniques work betterand more efficiently are only now in 2015 being researched. Sciencesuggests that the natural firing of these action potentials that occursin these contracted and extended positions is enhanced when the externalstimulation is timed precisely with the bodily movements. These studiesare not just anecdotal, but show real objective improvements inperformance.

With research, it is now understood that, in most people, concentriccontractions are best promoted by lower frequencies and higheramplitudes, while eccentric contraction is best promoted by higherfrequencies and low-mid-range amplitudes. This typical pattern can varyper person based on the degree of their training and neurologicaldevelopment. Because the settings are different in each individual,research has also developed techniques to establish a baseline for eachindividual by performing a set of diagnostic tests that informs thetechnician and the machines what initial settings are required and whatforms of timed interval settings are best for each exercise.

Example 6

The goal is the match the natural action potential produced by the bodywith the reproduced action potentials by predicting that the naturalaction potential will exponentially increase, and thereby increasing thereproduced action potential exponentially. During a long squat exerciseover a period of 30 seconds, if the frequency of the second pulsedelectrical current is matched to the natural action potential,significant improvement in muscle efficiency is found by over 15%compared to controls. The method involves varying the frequency over alonger period during a diagnostic stage wherein a match is made. A matchis made when there is an increase in the parameters (discussed above,such as heart rate variability, blood pressure, breathing, perspirationand subjective input) to an exercise that especially contracts thatmuscle. FIG. 15A shows how the frequency in a normal squat exercise canalter during a 30 second squat in healthy patient. Line 1501 is curvedupwards in an exponential way such that the needed frequency at higherrates of the exercise is needed. FIG. 15B shows how sending a “priorart” direct current pulse 1502 that is constant can incidentally hit thenatural curve at 1503. FIG. 15C is a representation of what turning themachine on and off can do—by turning the on/off switch the incidentalhits can actually occur more frequently, and thus by performing certainexercises at certain frequencies and changing them can mimic the naturalaction potential more closely rather than sending anuncharacteristically similar frequency. Intersections at 1504, 1505, and1506 shows how carrying the on/off switch can produce interactions thatcoincide more frequently with the natural action potential than in 15B.FIG. 15D involves a diagnostic testing of the patient such that feedbackresults in isolating the frequency pattern, and once the frequencypattern is stored, it can be reproduced during the squat exercises, andas shown in the intersections of 1508, 1509, and 1510, the frequency canbe narrowed with the feedback such that during exercises, a match can bemade of the reproduced frequency and the natural frequency as shown in1507 pathway. Such ability to mimic the natural action potential hasyield in higher rates of muscle efficiency which has resulted in fasterrecover rates from injuries and faster development of muscles intraining.

Example 7 utilizes design custom circuit and firmware to controlelectrical output of both dual signals and to control the environment inthe soundwave frequencies. The use of multiple frequencies wherein oneof the frequencies is a carrier wave that allows the second electricalcurrent to penetrate and reach desired nerves is performed usingconventional machines that can vary the frequencies, as discussedthroughout this disclosure and are contemplated in prior art machines,such as U.S. Pat. Nos. 5,107,835 and 5,109,848 machines. But thesemachines do not contemplate the use of precise waveforms that mimic moreclosely natural waveforms, nor do they utilize components with low noiseusing precise components for delivery of sound waves.

The music industry is filled with precise sound equipment made to reducenoise, and although it is unconventional to use sound equipment forneuromuscular stimulation devices, the development of neuromuscularstimulation devices using music internal components, such astransformers made for lower 0 to 1000 hz frequencies allows for acleaner signal with a reduction of noise, which is vital in devicesaimed precisely to stimulate muscle contractions.

The system 1701 is powered using standard 120V 60 Hz AC power via anexternal wall-wart power supply or internal AC-to-DC conversion. (notpictured) The device 1701 pictured in FIG. 17 will have a mastershut-off switch 1702 and will be modular in that each channel will becontrolled individually through panel-mount controls. Channel outputsare the sum of two waveforms, a high and low frequency, with the outputbeing capped at a pre-determined maximum value. A digital processorsynthesizes the waveforms for output and will pass the results throughdigital-to-analog conversion and amplification stages. The outputamplitude cap performs on the processor, and will also be clamped byhardware for redundancy. Firmware was developed using developmentenvironments MPLAB X and Microchip in parallel with the sourcing of theassembled circuit boards.

A breadboard circuit was designed that utilizes digital waveformsynthesis for creation of the stimulation waveform. The power stageconsists of an audio amplifier driving output transformers 1802 in FIG.18 which isolates the user electrodes from the digital electronics,earth ground, and input power. This stimulation topology offers a widerange of possibilities regarding waveform shape, input powerrequirements, and output power levels, lending to efficient design ofinstruments meeting varying application requirements. For example,waveform shape can be changed in firmware by simply reprogramming thedevice. Output power can be adjusted by either scaling the amplitude ofthe synthesized waveform, or by reducing the amplification of the audioamplifier. A preliminary circuit schematic is shown in FIG. 19. Theschematic drawing illustrates the design of the waveform output stages.A microcontroller (not depicted) would control the LTC2641Digital-to-Analog Converter (DAC) using the Serial Peripheral Interface(SPI) bus standard. The waveform created by the DAC passes through alow-pass RC filter and is then A/C coupled into both input channels of astereo audio amplifier. Amplifier output, gain, and fault conditions arecontrolled and monitored by the microcontroller. The output of eachaudio amplifier channel passes through an EMI filter and a fuse beforebeing connected to one side of the output transformer through connectorsP5 and P6. Electrodes are connected to the opposite side of the output1702 that are connected to the transformers 1802.

It is known to use load analogous to the human body—such as a simple RCcircuit as described in U.S. Pat. No. 5,109,848. LCD screen andcorresponding LCD internal component 1803 can be programmed to offervarious pictures of electrode placements on the bodies or videos ofvarious exercise movements that correspond with various exercises androutines consistent with descriptions in this disclosure.

The timing can be varied as the exercises can vary. There are variancesin ways to compare the exercise and the contraction of the muscles withthe needed frequencies, but because individuals are all different, it isbest to create an individual baseline at each session or during previoussessions. Conventional machines that can vary the frequencies arecontemplated in prior art machines, such as U.S. Pat. Nos. 5,107,835 and5,109,848 machines, but these machines do not contemplate theharmonizing of the second set of direct currents with the actionpotential, and standardizing efficiency model based onobjective/subjective measures of matching a variance of a reproducedaction potential with the real action potential during precise movementsthat involves the use of those muscles.

Clinical studies and patient data have shown significant muscleefficiency improvements that have led to the treatment and properhealing in over 90% of the cases for the following injuries:

-   -   Disc bulges, herniations of the cervical and lumbar spine    -   Rotator cuff sprains, strains, and tears    -   Elbow tendon and ligament injuries, including tennis elbow,        golfer's elbow, and UCL tears (the injury for which Tommy John        surgery is often required)    -   Sacroiliac Joint Dysfunction    -   Pain from Degenerative Joint Disease in the Hip and Knee    -   Strained/Torn Muscles    -   Non-surgical rehabilitation of torn knee meniscus    -   Ankle Sprains/Strains/Tears    -   Plantar Fascitis

Further, the training that involves the more efficient use of muscles byusing various electrodes that trigger activation of the body's reducedmuscles has proven to improve muscle mass, strength, flexibility, speed,and endurance in many different sports, including the successfultraining of athletes in the following fields:

-   -   Football, Baseball/Softball, Basketball, Soccer, Hockey,        Volleyball, Swimming    -   Track and Field    -   Dance—Ballet, Modern Dance, Competitive Cheerleading    -   Powerlifting and Olympic Lifting    -   Bodybuilding    -   Car/Motorcycle Racing    -   Wrestling, Martial Arts    -   Gymnastics and Diving    -   The so-called “Extreme Sports” like Skateboard, Motocross,        Wakeboarding, etc.    -   Mountain Climbing and Rock Climbing

Because enhancing muscle efficiency can enhance the performance ofmuscles, increased muscle efficiency has led to clinically validatedimprovements in performance for participants in many activities andsports. For example, let's take the common bench press. Traditionalbench pressing typically only strengthens the pressing muscles, like thepectorals, front deltoids, and triceps. An overlooked key to thismovement is actually the pulling muscles, those of the upper back andbiceps. When they work correctly, these muscles can pull the pressingmuscles into proper position so that they are lengthened out, loadedlike a bow and arrow. This is important, because these lengthened musclecan absorb much more force to protect the shoulder and elbow joints.When properly lengthened, they will also produce much more force andallow more weight to be lifted in the pressing phase. The presentinvention can be applied to facilitate both the lengthening of thepressing muscles, and also the ability of the pulling muscles to pullinto the correct position to promote that lengthening.

In another embodiment of the invention there is another form ofdetermining muscle efficiency by determining the locations of a musclethat experience the least efficient connection to the brain and thus arereduced in efficiency. The method may involve applying sound wavefrequency electrical currents in a location A of a muscle and thenidentifying a location on a precise location of a muscle where there isassociated a certain level of discomfort and then relocating theapplication of sound wave frequency currents to a location B and thencomparing the discomfort from location A to location B and determiningwhether location A or location B was higher. Further a larger number oflocations can be labeled, which may be XY axis of a particular muscle orin small or odd shaped muscles, each muscle only needs a consistentmanner to label and show patients the level and degree of inefficiency.By creating different locations with varying degrees of response fromthe currents, a map can be made (like a topographic map) showing morespecifically the location of the inefficiency in muscle that is beingtargeted.

A further embodiment of the invention involves the use of theseelectrical currents to be applied specifically during muscle extensionexercises. In this example, a stretch position, like a lunge positioninvolves the use of the quads, hamstrings, hip flexors, and glutealmuscles. When the muscles in the back leg are fully extended, the quadsand hip flexors must eccentrically contract to absorb force and protectthe knee, hip, and lower back. Applying the present invention enhancesthe ability of the brain to control these lengthened muscles, which thenallows the body to be more stable at greater ranges of motion. Theresult is improved flexibility in way that is safer than traditionalstretching, because in this method the muscles are lengthened and canabsorb force rather than bracing against the support of ligaments andother connective tissue as happens in traditional stretching.

While an example of suitable hardware is provided above, the inventionis not limited to being implemented in any particular type of hardware.

Further, it should be recognized that embodiments of the presentinvention can be implemented via computer hardware or software, or acombination of both. The methods can be implemented in computer programsusing standard programming techniques-including a computer-readablestorage medium configured with a computer program, where the storagemedium so configured causes a computer to operate in a specific andpredefined manner—according to the methods and figures described in thisSpecification. Each program may be implemented in a high levelprocedural or object oriented programming language to communicate with acomputer system. However, the programs can be implemented in assembly ormachine language, if desired. In any case, the language can be acompiled or interpreted language. Moreover, the program can run ondedicated integrated circuits programmed for that purpose.

Further, methodologies may be implemented in any type of computingplatform, including but not limited to, personal computers,mini-computers, main-frames, workstations, networked or distributedcomputing environments, computer platforms separate, integral to, or incommunication with charged particle tools or other imaging devices, andthe like. Aspects of the present invention may be implemented in machinereadable code stored on a storage medium or device, whether removable orintegral to the computing platform, such as a hard disc, optical readand/or write storage mediums, RAM, ROM, and the like, so that it isreadable by a programmable computer, for configuring and operating thecomputer when the storage media or device is read by the computer toperform the procedures described herein. Moreover, machine-readablecode, or portions thereof, may be transmitted over a wired or wirelessnetwork. The invention described herein includes these and other varioustypes of computer-readable storage media when such media containinstructions or programs for implementing the steps described above inconjunction with a microprocessor or other data processor. The inventionalso includes the computer itself when programmed according to themethods and techniques described herein.

Computer programs can be applied to input data to perform the functionsdescribed herein and thereby transform the input data to generate outputdata. The output information is applied to one or more output devicessuch as a display monitor. In preferred embodiments of the presentinvention, the transformed data represents physical and tangibleobjects, including producing a particular visual depiction of thephysical and tangible objects on a display.

Further, throughout the present specification, discussions utilizingterms such as “calculating,” “determining,” “measuring,” “generating,”“detecting,” “forming,” or the like, also refer to the action andprocesses of a computer system, or similar electronic device, thatmanipulates and transforms data represented as physical quantitieswithin the computer system into other data similarly represented asphysical quantities within the computer system or other informationstorage, transmission or display devices.

The invention has broad applicability and can provide many benefits asdescribed and shown in the examples above. The embodiments will varygreatly depending upon the specific application, and not everyembodiment will provide all of the benefits and meet all of theobjectives that are achievable by the invention.

Further, whenever the terms “automatic,” “automated,” or similar termsare used herein, those terms will be understood to include manualinitiation of the automatic or automated process or step.

In the following discussion and in the claims, the terms “including” and“comprising” are used in an open-ended fashion, and thus should beinterpreted to mean “including, but not limited to . . . .” The term“integrated circuit” refers to a set of electronic components and theirinterconnections (internal electrical circuit elements, collectively)that are patterned on the surface of a microchip.

To the extent that any term is not specially defined in thisspecification, the intent is that the term is to be given its plain andordinary meaning. The accompanying drawings are intended to aid inunderstanding the present invention and, unless otherwise indicated, arenot drawn to scale.

Although the present invention and its advantages have been described indetail, it should be understood that various changes, substitutions, andalterations can be made to the embodiments described herein withoutdeparting from the spirit and scope of the invention as defined by theappended claims. Moreover, the scope of the present application is notintended to be limited to the particular embodiments of the process,machine, manufacture, composition of matter, means, methods, and stepsdescribed in the specification. As one of ordinary skill in the art willreadily appreciate from the disclosure of the present invention,processes, machines, manufacture, compositions of matter, means,methods, or steps, presently existing or later to be developed thatperform substantially the same function or achieve substantially thesame result as the corresponding embodiments described herein may beutilized according to the present invention. Accordingly, the appendedclaims are intended to include within their scope such processes,machines, manufacture, compositions of matter, means, methods, or steps.

We claim as follows:
 1. A method of enhancing muscle efficiency in amuscle comprising: applying a first set of current pulses that arepulsed at a first set pulse rate between 20 Hz and 20,000 Hz to a targetmuscle, wherein the first set of current pulses acts as a carrierfrequency; applying a second set of current pulses in combination withthe first set of current pulses to the target muscle, wherein the secondset of current pulses have a resting period voltage level and adepolarization crest and a repolarization valley that dips below theresting period voltage level and a second set pulse rate between 1 Hzand 1000 Hz; applying the first set of current pulses and the second setof current pulses and increasing amplitude of the depolarization crestduring performance of lengthening movement for eccentric elongation ofthe target muscle to stimulate the target muscle contraction, increasework of the muscle during the lengthening movement, and to stimulatesensory receptors sensing changes in muscle length and increases intissue load during eccentric muscle contractions in the lengtheningphase of the movement where the increased signal from the sensoryreceptors increases an ability of a patient to use the target musclemore efficiently.
 2. The method of claim 1 wherein the pulse ratefrequency of the second set of current pulses can be increased duringthe movement to lengthen the target muscles to promote eccentricelongation of muscles during the lengthening phase of the movement.
 3. Amethod of claim 1, further comprising: measuring the level of workperformed by a muscle by increasing the voltage power of the first andsecond set of current pulses applied on said muscle and comparing withcorresponding measurements of maximum heart rate, heart ratevariability, average heart rate, blood pressure measurements, oxygensaturation level measurements, breathing rate, and galvanic skinresponse measurements of perspiration level in the patient performingthe lengthening movement.
 4. The method of claim 1 wherein the deliveryof first set of current pulses and second set of current pulses duringapplication to contract the target muscles is done using a first set ofelectrodes and a second set of electrodes.
 5. A method of enhancingmuscle efficiency in a muscle comprising: applying a first set ofcurrent pulses that are pulsed at a first set pulse rate between 20 Hzand 20,000 Hz to a target muscle, wherein the first set of currentpulses acts as a carrier frequency; applying a second set of currentpulses in combination with the first set of current pulses to the targetmuscle, wherein the second set of current pulses have a resting periodvoltage level and a depolarization crest and a repolarization valleythat dips below the resting period voltage level and a second set pulserate between 1 Hz and 1000 Hz; applying the first set of current pulsesand the second set of current pulses to contract the target muscle andstimulate sensory receptors sensing eccentric muscle contraction duringelongation, wherein the contraction of the target muscle is an eccentricmuscle contraction and is performed with movement that lengthens thetarget muscle; and increasing the pulse frequency of the second set ofcurrent pulses to promote eccentric elongation of muscles andstimulation of the sensory receptors sensing changes in muscle lengthand increases in tissue load during the eccentric muscle contraction inthe lengthening phase of the movement where the increased signal fromthe sensory receptors increases an ability of a patient's body to usethe target muscle more efficiently.
 6. The method of claim 5 wherein thevoltage amplitude of the second set of current pulses can be increasedor decreased during the movement to increase resistance during eccentricelongation of muscles during the lengthening phase of the movement.
 7. Amethod of claim 5, further comprising: measuring the level of workperformed by a muscle by increasing a voltage power of the first andsecond set of current pulses applied on said muscle and comparing theresults with corresponding measurements of maximum heart rate, heartrate variability, average heart rate, blood pressure measurements,oxygen saturation level measurements, breathing rate, and galvanic skinresponse measurements of perspiration level in a patient duringperformance of the movement that lengthens the target muscle.
 8. Themethod of claim 5 wherein the delivery of first set of current pulsesand second set of current pulses during application to contract thetarget muscles is done using a first set of electrodes and a second setof electrodes.
 9. The method of claim 5 wherein the pulse rate frequencyof the second set of current pulses can be increased during the movementto lengthen the target muscles to promote eccentric elongation ofmuscles during lengthening or decreased during the movement to promoteconcentric shortening of muscles in the opposite shortening phase of themovement.
 10. The method of claim 5 wherein the pulse rate frequency ofthe second set of current pulses can be decreased during the movement topromote concentric shortening of muscles in the opposite shorteningphase of the movement.
 11. The method of claim 1 wherein the pulse ratefrequency of the second set of current pulses can be decreased duringthe movement to promote concentric shortening of muscles in the oppositeshortening phase of the movement.